Stabilized Uncoated Particles of Reversed Liquid Crystalline Phase Materials

ABSTRACT

Uncoated particles of reversed cubic phase or reversed hexagonal phase material containing an active disposed within are provided. The uncoated particles have an ionic charge that is sufficient to stabilize them in dispersion in a liquid, e.g. a polar solvent. The active that is disposed within the particles may be, for example, a pharmaceutical or nutriceutical compound.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is claims priority to U.S. Provisional PatentApplication 60/509,255 filed Oct. 8, 2003, and the complete contents areherein incorporated by reference.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The invention generally relates to uncoated particles of reversed cubicphase or reversed hexagonal phase material containing an active. Inparticular, the invention provides uncoated particles having an ioniccharge that is sufficient to stabilize the particles in dispersion in aliquid, e.g. a polar solvent.

2. Background of the Invention

Many active compounds used in pharmaceutical, nutritional,nutriceutical, environmental, and industrial uses are either insolublein water, or perform better when delivered in some sort of protective,targetable, and/or otherwise functional matrix. In the case ofpharmaceuticals, it is generally recognized that microparticles canprovide robust matrices for drugs by various routes of administration,provided they are of appropriate size, stable in dispersion, andcomposed of excipients that are acceptable for that route. However, inaddition to solubilizing and/or protecting the active compound foradministration and/or in circulation, it would be advantageous for amicroparticle to play an active role in the delivery and absorption ofthe active, a goal that has been a stumbling block for a number ofpotentially useful particulate and droplet-based vehicles.

For the case of pharmaceutical actives that are of low solubility inwater, solubilization of such drug compounds is made challenging by thevery limited selection of solvents and structured liquids that areapproved by regulatory bodies for use at levels that would be requiredto solubilize the drug. Furthermore, water-miscible liquid excipients,most notably ethanol, are of limited value since, even when the drug issoluble in neat ethanol, for example, it will often precipitate uponcontact with water, such as with either diluent water for injection orin the aqueous milieu of body fluids, such as blood.

Nanostructured lyotropic liquid crystalline phases of the reversedtype—namely reversed cubic and reversed hexagonal phases—have beendeveloped as excellent solubilizing matrices for both poorly-solublecompounds, and for such delicate compounds as proteins and otherbiomacromolecules. U.S. Pat. No. 6,482,517 (Anderson, Nov. 19, 2002) andU.S. Pat. No. 6,638,621 (Anderson, Oct. 28, 2003), the contents of whichare incorporated in their entireties by reference, disclose, among otherthings, effective compositions and methods for producing such lyotropicliquid crystalline matrices. These particles are coated with solidmaterials.

A pioneer in surfactant phase behavior, P. A. Winsor, describedparticles of cubic phase coated with a nanostructured liquid phase,which in accordance with current knowledge was probably an L3 phase. SeeLiquid Crystals & Plastic Crystals, Vol. 1, eds. G. W. Gray and P. A.Winsor (1974), Ellis Horwood Ltd., page 224, as well as Balinov, Olssonand Soderman (1991) J. Phys. Chem. 95:5931. Larsson, in 1989, describedreversed cubic phase particles with lamellar liquid crystalline phasecoatings. See Larsson (1989) J. Phys. Chem. 93(21) 7304.

U.S. Pat. No. 5,531,925 (Landh et al., Jul. 2, 1996) likewise describesparticles of reversed cubic or reversed hexagonal phase which require asurface phase of either lamellar liquid crystalline, lamellarcrystalline, or L3 phase, in order to disperse the particles. Thecoating is referred to in that disclosure as a “surface phase”, or“dispersible phase”, thereby teaching, first, that it is a distinct,separate phase from the reversed liquid crystalline interior, andsecond, that the reversed liquid crystalline phase interior is itselfnot a dispersible phase. The L3 surface phase in that disclosure isdescribed as being “anchored to the bi- or mono-layer of the interiorphase” (column 7, lines 59-60).

U.S. Pat. No. 6,071,524 describes compositions in the form ofdispersions containing: (a) 60 to 98% by weight of an aqueous phase and(b) 2 to 40% by weight of an oily phase dispersed in the aqueous phase,the oily phase being dispersed and stabilized by using cubic gelparticles. The particles are essentially formed of 0.1 to 15% by weight(relative to the total weight of the composition) of at least oneunsaturated fatty acid monoglyceride having a C16-C22 unsaturated fattychain in a mixture with phytanetriol, and 0.05 to 3% by weight relativeto the total weight of the composition of a dispersing and stabilizingagent. The agent is a surface active substance, water-soluble at roomtemperature, containing a linear or branched, saturated or unsaturated,fatty chain having 8 to 22 carbon atoms. The patent also describesmethods of making such compositions. A minimum of threethermodynamically distinct phases are present in such a mixture, namelythe aqueous exterior phase, the cubic gel particles, and the oil phasecontaining the active. The active substance (drug, cosmeceuticalcompound, etc.) is present in the dispersed oily phase, and in factsubstantially localized in the oily phase. Such systems, emulsions inwhich lipid or surfactant monolayers, multilayers, lamellar ornon-lamellar liquid crystalline domains or lamellar crystalline domainsstabilize droplets of one fluid in another, suffer from poor suitabilityfor targeting, shelf-life limitations (creaming, breaking of emulsions,etc.), and other problems well known in the art of emulsions. Andemulsions or droplet systems in which each droplet is surrounded by aplurality of particles of another material or phase, all undergoingindependent diffusion around the droplet (and, by definition, areseparated from one another by intervening fluid layers), suffer fromgaps between the particles that compromise the ability of the materialto control the egress of active out of, or ingress of confoundingfactors into, the droplet. Furthermore, with such a system wherein theplurality of particles surrounding the droplet are derived fromlyotropic liquid crystals, as in U.S. Pat. No. 6,071,524, in the body ofan animal these particles can readily become independent of thedroplets, such that the droplets, which contain the vast majority of theactive, do not reap the potential benefits (as discussed herein) of theliquid crystalline particles. Although the “cubic gel particles” of U.S.Pat. No. 6,071,524 are designed to aggregate at the surface of the oildroplets, in a pharmaceutical application the high dilution factors andshear forces, together with the myriad of biochemical conditions andprocesses encountered by a droplet, could readily strip the droplets oftheir intended coating. Another limitation of the invention described inU.S. Pat. No. 6,071,524 is that neither the monoglycerides nor thephytanetriol (nor many of the other surfactants used in the reportedembodiments) is approved for use in injectable pharmaceutical products,and indeed monoglycerides are known to be extremely toxic uponinjection.

U.S. application 2002/0153509 (Lynch et al, published Oct. 24, 2002)describes compositions in which charged compounds are used as “anchors”(“tethers”), serving to anchor active compounds or targeting compoundsto cubic phases, sometimes in particulate form. For example, it isstated in the disclosure of 2002/0153509 that the inclusion of an anchorsuch as a cationic surfactant could increase the amount of active drugin the cubic phase in proportion to the amount of surfactant (e.g.,paragraph 0099), in accordance with the schematic picture shown in FIG.2 of that disclosure which depicts an anionic ketoprofen moleculeassociated with the head group of a cationic surfactant (and situated onthe polar side of the polar-apolar interface). The anchor's purpose isto bind a drug molecule, on a 1-to-1 molecule basis.

It would be desirable to have improved microparticles for drugsolubilization and protection that are of an appropriate size, stable indispersion, and composed of excipients that are acceptable foradministration via a variety of routes. In addition, it would bedesirable to have improved microparticles that also play an active rolein the delivery and absorption of the drug.

SUMMARY OF THE INVENTION

As discussed in more detail herein, particles of reversed lyotropicliquid crystalline phase materials can exhibit high potential totransport active compounds across a variety of barriers such as cellmembranes, particularly in the case of the reversed bicontinuous cubicphases, by virtue of their unique nanoporous structures and associatedcurvature properties. The reversed cubic and reversed hexagonal liquidcrystalline phases can be of very low solubility in water, meaning thatthey maintain their integrity as vehicles upon entry into the body thusavoiding drug precipitation. Thus, with superior solubilizing andsequestration properties, as well as integrity in water, these materialsshow a great deal of promise in fields such drug delivery. However, thispotential has remained largely untapped due to the tacit assumption thatsuch particles must be coated in order to be stable in dispersion.

In the present invention, the full potential of this transport activitycan be tapped within the context of stable particle dispersions, firstthrough the realization that uncoated particles of such phases arehighly desirable for their transport and absorption-enhancingproperties, and second through the realization that ionically charged,bilayer-associated compounds with appropriate chemistries andconcentrations can stabilize such particles as uncoated particles bycreating strong electrostatic surface potentials—particle zetapotentials. In particular, it is taught herein that zeta potential is akey parameter for establishing such stabilization, and that a zetapotential of greater than or equal to about 25 mV, or more preferablygreater than about 30 mV, in magnitude is an important requirement forsuch a system. Likewise, a zeta potential of less than −25mV or lessthan −30mV in magnitude is useful for stabilization.

The invention thus provides stable, uncoated particles formed ofreversed lyotropic liquid crystalline materials, e.g. reversed cubic orreversed hexagonal liquid crystalline material. The particles are“uncoated” in that the liquid crystalline material of which theparticles are formed is in direct contact with the medium in which theparticles are dispersed, i.e. the outer periphery of an individual,dispersed particle is not shielded from the medium (for example, anaqueous liquid phase) in which the particles are dispersed. No coatingintervenes between the particle and the medium, or between a particleand other particles. Rather, the particles are repelled from one anotherand are held in dispersion in the medium by strong electrostatic surfacepotentials. Such strong electrostatic surface potentials are created byproper choice of the “ingredients” which are combined to make up theliquid crystalline material of which the particles are formed, as taughtherein. In general, the ratio by weight of particle to liquid phasemedium is in the range of between about 1:2 to about 1:1000. Theparticle size is between about 10 nanometers (the order of magnitude ofa single unit cell of reversed liquid crystalline material) and 100microns, preferably between about 40 nm and 10 microns, and mostpreferably (at least for injectable products) submicron, meaning lessthan one micron in effective diameter. Particles that can be passedthrough a 0.22 micron filter, or extruded similarly, are especiallypreferred since this sterilizes the product.

In some embodiments of the invention, an active compound, typicallythough not always a pharmaceutical compound, is dissolved or dispersedor otherwise incorporated within the liquid crystalline phase materialitself. Preferably, in this embodiment, the active compound and theliquid crystalline material form an intimately-associated, integratedunit, i.e. the active compound is part of the liquid crystal. Oneadvantage of such a particle is that the active compound reaps thebenefit of the absorption-promoting capabilities of the liquid crystal,in a manner that is superior to particle configurations describedelsewhere, where the active is present primarily outside the liquidcrystal, or inside a liquid crystal particle that is covered with aninterfering coating. Indeed, it is envisioned that in many cases, themajority of actives will remain associated with the liquid crystal up tothe point where the liquid crystal integrates with, for example, atargeted cell membrane, thereby eliminating the need for the active todissolve in an aqueous biological fluid (e.g., blood, intestinal fluid)en route to cellular uptake. If the particle is taken up by endocytosis,then the same ability to fuse with biomembranes could play a key role incircumventing a limitation that applies to liposomes, namely that ofentrapment inside endosomal compartments and resulting poor delivery tothe intracellular site(s). It is also of major impact herein that thiscan all be accomplished within the context, and extreme restrictions, ofinjectable formulations including intravenous pharmaceuticalformulations.

In another embodiment of the invention, the active agent or compound isnot part of the liquid crystalline material that forms the uncoatedparticle, but is either a liquid that is embedded within the uncoatedparticle, or is solubilized in a liquid that is embedded, dissolved,dispersed or otherwise incorporated within the uncoated particle. In yetanother embodiment, the active agent is dispersed inside the uncoatedparticle in the form of microcrystals of the compound.

Thus, it is an object of this invention to provide administrableactive-loaded microparticles that take full advantage of theabsorption-promoting and drug-solubilizing potential of reversed cubicand reversed hexagonal liquid crystalline phase microparticles,undiminished by effects of coatings.

It is an object of this invention to provide administrable active-loadedmicroparticles that exhibit direct, unhindered interactions withbiomembranes which can strongly promote absorption and/or allowtargeting.

It is another object of this invention to provide stable dispersions ofsuch active-loaded lyotropic liquid crystalline microparticles forinjection.

It is another object of this invention to provide design criteria andcompositions that will yield stabilized particle dispersions of reversedliquid crystalline phase material.

It is another object of this invention to provide experimental criteriaand procedures by which to determine whether a particular compositionwill yield stabilized particle dispersions of reversed liquidcrystalline phase material.

It is another object of this invention to provide compositions with thenecessary physicochemical properties to yield sufficient surface chargestabilization.

It is another object of the invention to provide methods for stabilizinguncoated particles of reversed liquid crystalline phase materials.

It is another object of this invention to provide a method for treatinga mammal with a pharmaceutical or nutriceutical active compound byadministering a dispersion of uncoated particles of reversed liquidcrystalline phase material.

It is another object of this invention to provide nanocrystal drugformulations in which the stabilizing matrix can serve the additionalfunctions of enhancing drug absorption and solubilizing other usefulexcipients for intimate association with the drug.

It is another object of this invention to provide compositions thatyield charge-stabilized particles and dispersions thereof uponreconstitution with water.

Further, it is an important object of this invention to provide newcompositions and methods for the delivery of cancer therapeutic agents,local anesthetic and general anesthetic agents, and anesthetic reversalagents. These include in particular propofol, alphaxalone, alfatalone,alphadolone, eltanolone, propanidid, ketamine, pregnanolone, etomidate,and other general anesthetics; bupivacaine, lidocaine, procaine,tetracaine, mepivacaine, etidocaine, oxybuprocaine, cocaine, benzocaine,pramixinine, prilocaine, proparacaine, ropivicaines, chloroprocaine,dibucaine and related local anesthetics; SN-38 and relatedcamptothecins; paclitaxel and related taxanes; doxonibicin, idarubicin,daunorubicin and related rubicins; amphotericin B; coenzyme Q10;steroids and steroidal anti-inflammatory agents; nonsteroidalanti-inflammatories (e.g., salicylates, para-aminophenol derivatives(e.g., acetaminophen), fenomates, proprionic acid derivatives (e.g.,naproxen, ibuprofen, etc.); analgesics; antipyretics; sedatives (e.g.,benzodiazepines such as diazepam); hypnotics (e.g., intravenousanesthetics and barbiturates); opiates; cannabinoids; and proteins(e.g., insulin and erythropoietin)(it being understood that a widevariety of amides and esthers may have application in the presentinvention). Of particular importance is the general anesthetic agentpropofol, which is supplied in formulations that suffer from problems ofburning on injection, microbial contamination, and high lipid loads.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a schematic of a dispersion according to the presentinvention.

FIG. 2 shows a schematic of the electrostatic situation in arepresentative particle of the instant invention, with a net negativesurface charge.

FIG. 3 shows the resulting measured zeta potential distribution, usingthree angles of measurement for the dispersion described in Example 1.

FIG. 4 shows the zeta potential distribution measured for a dispersionin the presence of excess water described in Example 2.

FIG. 5 shows the phase behavior in the presence of excess water asanalyzed with a polarizing optical microscope for the dispersiondescribed in Example 2.

FIG. 6 shows the zeta potential data for the dispersion described inExample 5.

FIG. 7 shows the zeta potential data for the dispersion described inExample 6.

FIG. 8 shows the zeta potential data for the dispersion described inExample 7.

FIG. 9 shows the zeta potential data for the dispersion described inExample 8.

FIG. 10 shows the zeta potential data for the dispersion described inExample 10.

FIG. 11 shows the zeta potential data for dantrolene sodium with onlybenzalkonium (i.e. no cubic phase is present) as described in Example10.

FIG. 12 shows the zeta potential data for the dispersion described inExample 11.

FIG. 13 shows the zeta potential data for the dispersion described inExample 12.

FIG. 14 shows the zeta potential data for the dispersion described inExample 13.

FIG. 15 shows the particle size data for the dispersion described inExample 21.

FIG. 16 shows the zeta potential data for the dispersion described inExample 21.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS OF THE INVENTION

The inventor has demonstrated the relationship between curvatureproperties of lipids, and their tendency to promote porosity in bilayersand to form reversed cubic and other reversed phases. See Anderson D.M., Wennerstrom, H. and Olsson, U., J. Phys. Chem. 1989, 93:4532-4542.To summarize a crucial aspect of this, if one assumes a mathematicalmodel in which the bilayer thickness is constant, and that the bilayermidplane is twice differentiable, one can show first that, in order tominimize unfavorable curvature energies, the midplane must have zeromean curvature throughout. Next, under these conditions one can thenshow that if the average mean curvature at the polar-apolar interface istoward water—as it is in a reversed liquid crystalline phase—then theintegral Gaussian curvature is significantly negative. Negative integralGaussian curvature then implies porosity in the bilayer system. Aconclusion of the full analysis drawn by the inventor is that, if acomposition which assembles into a porous bilayer phase, such as areversed cubic phase, begins to exchange material with a membrane, suchas a biomembrane, it can induce a local tendency for reversed curvature(curvature toward water at the polar-apolar interface), and therebyinduce porosity in the biomembrane. This can be of great importance inthe delivery of drugs across biomembrane barriers to absorption,constituting an inherent advantage of a reversed cubic or reversedhexagonal phase over a lamellar or liposomal material in the practice ofdrug delivery, particularly in the delivery of anticancer drugs andother drugs where absorption barriers are very significant problems intherapeutic treatment.

In view of this relationship, the tendency to induce or form porousmicrostructures is viewed in the present context as being advantageouswith respect to drug- and nutrient-delivery in particular, as well as inother applications, in that it promotes the integration of administeredlipid-based (or surfactant-based) microparticles with biomembranes thatotherwise form barriers to absorption. This is in sharp contrast withlamellar lipidic structures such as liposomes which show low curvature,and little or no porosity, and do not ordinarily show strong tendenciesto integrate with biomembranes. One very important aspect of this isthat it can also allow cubic phase materials to overcome efflux proteinssuch as P-glycoprotein (P-gp). The inventor recognizes it is crucial toprovide for as intimate contact as possible between the reversed liquidcrystalline phase material and any biological (or other) barriersinherent in the application of the invention. Examples of such barrierswhich are of particular interest as barriers that can be overcome by thepresent invention include: plasma membranes of cells that are sites ofdrug action; the blood-brain barrier; apical membranes of intestinalepithelial cells; macrophage membranes; neuronal cell membranes;intracellular membranes such as the mitochondrial membrane or thenuclear membrane; and buccal or nasal mucosal cell membranes.

However, while a number of methods have been developed for formulatingmicroparticles of reversed liquid crystalline phases, the inclusion of astabilizing coating phase has led to the development of particles withattentuated absorption-promoting properties, since the interactions withbiomembranes are then affected by the properties of the coating, ratherthan the reversed liquid crystalline phase itself. Thus, while suchcoatings often serve a useful function, in some cases the coating may beundesirable.

In this invention, drug-loaded microparticles of reversed cubic andreversed hexagonal liquid crystalline phases are dispersed in a liquidsuch as water, without any coating, thus permitting direct interactionsbetween the liquid crystal and biological barriers. In addition, thiscan be achieved using only components that arepharmaceutically-acceptable for injection, including intravenousinjection, a necessary requirement for the use of such dispersions incertain critical drug-delivery applications. This is achieved in thepresent invention by compositions containing ionically chargedbilayer-associated components that yield an electrostatic potential onthe particles sufficiently strong to stabilize the particle dispersionsagainst aggregation, flocculation, and fusion; as a rule this requires azeta potential greater than or equal to about 25 mV in magnitude, ormore preferably greater than about 30 mV in magnitude. The inventionthus represents a fundamental departure from particles, and teachings,of the prior art based on reversed liquid crystalline phases with acoating, i.e. in which an additional phase on the exterior of theparticle stabilizes dispersions of such particles.

U.S. Pat. No. 5,531,925 provides an example of the tacit assumption toprevious teachings that a coating a) is required to stabilize liquidcrystalline particles, and b) does not interfere with particle function.The particles described in U.S. Pat. No. 5,531,925 are coated withsurface phases comprising L3 phases and lamellar liquid crystallinephases or lamellar crystalline phases which are inherent obstructions tofunction. These surface phases, in close analogy with liposomes based onlamellar liquid crystalline and lamellar crystalline phases, suffer froma number of drawbacks and limitations, most notably unfavorableinteractions with biomembranes that limit their ability to deliver theirpayload to cells. Indeed, not only do these intervening surface phasesimpede the entry of the vehicle into the target cell, but in addition,after entry—which typically requires endocytosis—the particle isentrapped in an endosome representing yet another barrier to delivery.Such limitations are well known in the field of liposome-baseddrug-delivery. They are particularly limiting in the case of injectabledrug formulations, where barriers to vehicle uptake by the target cellincrease the likelihood that the vehicle is taken up by unfavorable oreven toxicity-eliciting alternative mechanism, such as by the liver orthe immune system.

In the case of coatings consisting of L3 surface phases, the tendencyfor the L3 phase to exhibit only very limited absorption-favoringinteractions with biomembranes is probably due to its highly dynamicstructure, and/or its ability, and tendency, to very rapidly reorganizeinto a lamellar or lamellar-like structure, correlating with itsobserved shear-birefringence, the presence of a splitting in pulsed-NMRbandshape measurements, and its transformation into a lamellar phaseover time (see U.S. Pat. No. 5,531,925 column 7 lines 37-48 and column15 lines 5-36). Indeed, the “lubricating” effect of the L3 phases, whichis apparently what makes them effective as “dispersible phases” in themethods of U.S. Pat. No. 5,531,925, can be described as inducing atendency for L3-coated particles coming in near-contact to avoid fusion,due in part to the fluctuating, thermally-roiled nature of the liquid L3phase producing an effective repulsive force of considerable strength.The same repulsion appears to apply to particles coming in near-contactwith the walls of a container, correlating with a lack of adhesion and“slippery” flow noted by Landh with his dispersions of L3-coatedparticles. By extension, it would follow that L3-coated particles shouldby their very nature experience a strong fluctuation-induced repulsiveforce when approaching a biomembrane, and thus suffer limitations thathave plagued liposome technology, particularly in regard to cell entryand lack of absorption promotion. The long-circulating nature of theL3-coated particles, reported in the example of intravenous somatostatinin rabbits of U.S. Pat. No. 5,531,925 supports the notion that theseparticles do not tend to interact intimately with biomembranes, butrather stay in circulation by avoiding integration with membranes.

Contributing further to this fluctuation-induced force (which in thestudy of closely-related lamellar phases is referred to as the“undulation force”, well studied by W. Helfrich) are hydration-inducedforces arising from the highly hydrated L3 phase. The L3 phase quitegenerally exists at high water contents, nearly always at higher watercontents than any cubic phase(s) that is (are) close in compositionspace; Landh and Larsson note in fact that when an L3 phase and cubicphase are in equilibrium, that the characteristic dimensions of the L3phase are approximately twice those of the cubic phase, and thiscorresponds to considerably higher water content, a conclusion that isadditionally made obvious by the phase diagram itself where the watercontent in the L3 phase is higher than that of the cubic phase. It iswell known in the art that heavily hydrated surfaces experience aconsiderable repulsive force upon approaching a biomembrane. The highlypolyoxyethlyated (PEGylated), high-HLB surfactants that are present inlarge weight-fraction proportions in the L3 phases of the reportedembodiments in U.S. Pat. No. 5,531,925 are known to be very heavilyhydrated at ambient or body temperatures. In the instant invention, inthe case where the particles are stabilized by a negative zetapotential, this will give rise to a repulsive force upon near-contactwith a typical biomembrane, but due to the low magnitude of the zetapotential of a typically biomembrane, the force will be weak incomparison with the combined fluctuation and hydration-induced forces inthe L3-coated particle case. In cases of the current invention where apositive zeta potential stabilizes the particles, this will give rise toan attractive force. Hydration forces in the case of particles of thecurrent invention can be kept weak, as evidenced by the low watercontents of the reversed liquid crystalline phases even when thecharged, bilayer-associated compound is incorporated directly into theliquid crystalline phase, as shown in several of the cases reported inthe Examples section below.

The presence of another phase coating the surface of the aforementionedparticles can not only intervene and interrupt potentially favorableinteractions between the liquid crystal and biomembrane barriers toabsorption, but can also create numerous practical and experimentalproblems. Interpretation of in vivo performance and elucidation of themechanism of action of the formulation is of course complicated by thepresence of a coating, which can be of considerable impact in thedevelopment and application of an injectable pharmaceutical formulation.In the case of L3 phase coatings, even the existence of the L3 phase isdifficult experimentally to validate, much less characterize, asindicated for instance in lines 29-33 of column 15 of U.S. Pat. No.5,531,925; furthermore, as indicated on lines 41-45 of column 7, the L3phase is often metastable, and this can give rise topharmaceutically-unacceptable changes in structure over time, as provenin publications dealing with particles of Landh and Larsson: SeeGustafsson, Ljusberg-Wahren, Almgren and Larsson (1996), Langmuir.12(20):461 1. In addition, in the case of particles of the U.S. Pat. No.5,531,925 patent, compositions yielding such particles are limited tothose lying in 3-phase regions of the phase diagram where the interior,coating, and exterior aqueous phase are in thermodynamic equilibrium.Such 3-phase regions are often difficult to find experimentally and aretypically sensitive to material purity and other intensive variables.

Another valuable aspect of the current invention over such coatedparticles as those of U.S. Pat. No. 5,531,925 is the fact that thereversed liquid crystalline phase is the only lipid-based matrix in theparticle and thus the only location available within the particle for anactive compound, in contrast with particles coated by anotherlipid-based (or surfactant-based) phase, particularly an L3 phase. Whena second phase, the coating phase, is also available for the active, adegree of control is lost and this can compromise or even negate theeffect of one or more of the features that made the reversed liquidcrystalline phase the matrix of choice in the first place. For example,if the controlled poresize of the reversed liquid crystalline phase isbeing used to control either the efflux of a large-molecule active outof the liquid crystal, or the penetration of an adsorbing (e.g.,albumin) or degrading protein (e.g., protease, nuclease, glycosidase),then this is compromised if a significant fraction of the active ispresent in the coating phase; the effective poresize of the L3 phasecoating is known to be larger than that of the interior phase by afactor of two, typically. It is important to note in such an instancethat in general, components of these liquid crystalline phases includingthe active diffuse around within the particle, so that the active willbe located in the coating phase a certain fraction of the time, andduring these periods it may be susceptible to attack.

FIG. 1 shows a schematic of a dispersion of uncoated particles accordingto the present invention. The letters “D” indicate that drug (or moregenerally, active) is present in the reversed cubic phase or reversedhexagonal liquid crystalline phase particle. In the most preferredembodiment, the drug or active D is a component of the reversed cubicphase or reversed hexagonal phase. In alternative embodiments, the drugor active D is dissolved or dispersed or embedded or otherwiseincorporated within the particle. In one variation, the drug or active Dmay be incorporated in an oil phase that is positioned within theparticle.

FIG. 2 shows a schematic of the electrostatic configuration in arepresentative uncoated particle of the instant invention, with a netnegative surface ionic charge. The “+” signs represent cationic moietiesand the “−” signs represent anionic moieties, which in this case wouldinclude the charged, bilayer-associated compounds utilized in theinvention. As one moves away from the (anionically-charged) surface ofthe particle, the preponderance of negative charges diminishes. The zetapotential measurement measures the potential due to the excess of ioniccharges (in this case, anionic) at the shear plane, which is displacedfrom the particle surface. Nevertheless, at least in the conditions usedin the Examples below and quite broadly in the practice of thisinvention, the shear plane still lies within the Debye layer, which isat a distance (the Debye length) from the particle surface where thereis no longer a net excess of anions.

The following definitions will be helpful.

-   Uncoated particle: As used herein, an uncoated particle of reversed    cubic (or hexagonal) phase is a particle in which the outermost    material phase of the particle is a reversed cubic (or hexagonal)    phase, so that there is no other phase present exterior to and in    contact with this outermost material phase except for a single    liquid (usually aqueous) phase in which the particles are dispersed    (dispersion phase), and wherein the material of this reversed cubic    [hexagonal] phase is a single, contiguous and isolated mass of    material thus defining a single particle. In this definition    “isolated” means substantially not in contact with other such    particles except for the normal particle-particle collisions in the    course of Brownian motion.

The uncoated particle thus defined contrasts with U.S. Pat. No.6,482,517 in which there is a crystalline coating exterior to the liquidcrystalline phase, and also in contrast with U.S. Pat. No. 5,531,925 andthe work of P. A. Winsor cited above in which there is a distinct L3phase, lamellar phase, or crystalline lamellar phase exterior to (i.e.coating) the reversed liquid crystalline phase. As discussed herein, theL3 and lamellar coatings in particular are antithetical to the purposeof employing the particles in permeability enhancement for improved drugdelivery, and they may furthermore introduce other limitations andpractical problems.

It should be noted that this definition does not preclude thepossibility that, at a scale which is small compared to the thickness ofthe outermost material phase (usually the radius of the particle, unlessfor example an oil-core is present as per U.S. application Ser. No.10/176,112, which is herein incorporated by reference, or the particlecontains an embedded crystal), the nanoscale appearance at the surfaceof the outermost material phase does not represent the typicalappearance in the bulk of that material phase, because of surfacereordering or related effects, provided there is no extraneous phasepresent exterior to the liquid crystalline phase in the sense of theGibbs Phase Rule. As is well known in the art, surface energies caninduce reordering at the surface of a material that can change themicroscopic appearance, as for example a hemispherical end-cap coveringwhat would be a pore opening at the end of a cylinder in the reversedhexagonal phase. However, this does not indicate the presence of anotherphase, in the strict thermodynamic sense of a phase. To illustrate, at agiven temperature and pressure, by the Gibbs Phase Rule a two-componentlipid/water mixture can only exhibit two phases at equilibrium, andwhile the surface of a portion or particle of reversed hexagonal phasecould showy a nanoscale-thickness region that is rich in hemisphericalend-caps, with polar groups of the lipid in contact with an exteriorwater-rich phase (the second phase of the two present), this region doesnot constitute a third phase. (Although the term “interphase” has beenused to describe such regions, even users of that term will agree thatit does not represent a distinct thermodynamic phase as governed by thePhase Rule; rather, an interface, or interfacial zone, describes thesurface of the outermost material phase). In general, the thickness ofthis surface-reordered region will be about equal to or less than theunit cell lattice parameter, in the case of reversed hexagonal phase andreversed cubic phase materials. Thus, in particular, the thickness ofsuch a surface-reordered region (or “interphase”) will generally be lessthan about 30 nm, and usually less than about 20 nm.

In the case of the solid-coated particles revealed in U.S. Pat. No.6,482,517 where the interior phase is a reversed cubic or reversedhexagonal phase, it will be obvious to anyone skilled in the art thatthe material constituting the solid coating is a distinct phase from theliquid crystalline interior.

-   Polar, Apolar, Amphiphile, Surfactant, Polar-apolar interface,    Bicontinuous: The terms “polar”, “apolar”, “amphiphile”,    “surfactant”, “polar-apolar interface”, and “bicontinuous” as used    herein are taken to have the meaning given in U.S. Pat. No.    6,638,621, the complete contents of which is incorporated herein by    reference.-   Bilayer-associated, membrane-associated: A compound or moiety is    bilayer-associated if it partitions preferentially into a bilayer    over an aqueous compartment. Thus, if a bilayer-rich material such    as a reversed cubic phase material exists in equilibrium with excess    water and is placed in contact with excess water, and a    bilayer-associated compound or moiety is allowed to equilibrate    between the two phases, then the overwhelming majority of the    compound or moiety will be located in the bilayer-rich phase. The    concentration of the compound or moiety in the bilayer-rich phase    will be at least about 100 times, and preferably at least about    1,000 times, larger than in the water phase.

It is important to note that although the reversed hexagonal phases andreversed discrete or discontinuous cubic phases do not have a truebilayer as the fundamental structural unit, in the present disclosure wewill nevertheless use the term “bilayer-associated” to describecomponents that partition into the lipid-rich (or surfactant-rich)microdomains irrespective of whether such domains are considered“monolayers” or “bilayers”. The term “bilayer-associated” is thus moredirected to the partitioning of the compound in question than to theprecise nature of the lipid (or surfactant) region.

Besides targeting and bilayer-charging compounds, another component ofthe particle that can be bilayer-associated is the drug (or moregenerally, active) itself. For small molecules, this is preferred, sinceit means that the drug will tend to remain with the particle even whenthe particle is exposed to large volumes of biological fluids. However,drugs that partition preferentially into the aqueous channels of thereversed liquid crystalline material, including many if not mostproteins and other biomacromolecules, can be incorporated into particlesof the current invention, as can drugs that localize to comparableconcentrations in the aqueous and hydrophobic compartments. Indeed, oneimportant aspect of the invention which distinguishes it over typicalemulsions, for example, is the very large polar-apolar surface areas,which provide ample volume for drugs which have apolar groups orepitopes that prefer a hydrophobic milieu as well as polar groups thatprefer the hydrophilic milieu of the aqueous channels and headgroup-rich regions.

-   Hydrophobe-rich droplet; hydrophobe-rich phase: In some embodiments    of the instant invention, the reversed liquid crystalline phase    material will contain, in its interior, a droplet of a    hydrophobe-rich phase that is distinct from the reversed liquid    crystalline phase; this is not to be confused with hydrophobic    domains that are structural elements of the reversed liquid    crystalline phase itself. This hydrophobe-rich droplet will he of    size between about 20 nm and 100 microns, that will contain as a    major component a hydrophobe, thus a component of low solubility in    water (less than about 3%), and/or of high octanol-water partition    coefficent (Kow greater than or equal to about 10, more preferably    greater than about 100), in which are solubilized the active and    some fraction (perhaps very small) of each of the components of the    second volume. Thus, while thermodynamics dictates that this first    volume must contain at least a trace of lipid and the second volume    at least a trace of the hydrophobic liquid, the defining feature of    the first volume chemistry is that the ratio of hydrophobic liquid    to lipid is significantly higher than in the second volume. The    solubility of a given active in a mixture of hydrophobe and lipid is    typically a very strongly increasing function of an increasing    hydrophobe:lipid ratio, because the hydrophobe can generally be    chosen specifically for its ability to solubilize the particular    active whereas the choice of lipid has much more to do with its    ability to form liquid crystals (in the presence of the hydrophobe,    in particular). For example, whereas the solubility of the drug    paclitaxel in eugenol is over 15% by weight, its solubility in a    mixture of 42% egg phosphatidylcholine, 35% eugenol, and 23% water    is less than 1.5%; thus the addition of phospholipid and water to    the paclitaxel-in-eugenol solution induces precipitation of the    paclitaxel. The presence of the first volume can thus dramatically    increase the overall solubility of the active in the particle, and    can yield a substantial and pharmaceutically appropriate    concentration of active in cases where the solubility of active in a    lipid-rich liquid crystalline phase (in the absence of the first    volume) would be prohibitively low, that is, in cases where an    therapeutic amount of drug could not be solubilized in a    pharmaceutically acceptable amount of liquid crystal. These    requirements can be phrased in terms of phase behavior as follows.    There must exist a liquid crystalline phase in equilibrium with a    liquid phase which is rich in a hydrophobic liquid that solubilizes    the active. Furthermore, preferably there should exist a three-phase    equilibrium with these two phases in equilibrium with a polar    solvent-rich phase, which is usually a water-rich phase, often over    90% water.

This liquid phase will be hydrophobe-continuous, which is thegeneralization of the term of art “oil-continuous” to the case where thehydrophobe can be quite different chemically from what is commonlyreferred to as an “oil”. Thermodynamically, this liquid phase can be areversed micellar solution, a surfactant solution (whether dilute orotherwise, bearing in mind that every surfactant will have some non-zerosolubility even if it is vanishingly small), an oil-rich microemulsion,or an L3 phase (of the type referred to as L3*, in publications where L3and L3* are distinguished). These phases are well known in the art, andare discussed in detail in U.S. Pat. No. 6,482,517.

-   Pharmaceutically-acceptable: In the context of this invention,    “pharmaceutically-acceptable” generally designates compounds or    compositions in which each excipient is approved by the Food and    Drug Administration, or a similar body in another country, for use    in a pharmaceutical formulation, or belongs to a succinct class of    compounds for which a Drug Master File is on file with a government    regulatory agency, usually the FDA. This also includes compounds    that are major components of approved excipients, which are known to    be of low toxicity taken internally. A listing of approved    excipients, each with the various routes of administration for which    they are approved, was published by the Division of Drug Information    Resources of the FDA in January, 1996 and entitled “Inactive    Ingredient Guide”. The existence of a Dnig Master File at the FDA is    additional evidence that a given excipient is acceptable for    pharmaceutical use, at least for certain routes of administration.    For injectable products, a listing of approved excipients was    published in 1997. Sec Nema, Washkuhn and Brendel (1997) PDA J. of    Pharm. Sci. & Technol. 51(4):166. It should be added that there are    certain compounds, such as vitamins and amino acids, which are in    injectable products (typically for parenteral nutrition) as    “actives”, and are thus known to be safe upon injection, and such    compounds are considered herein as pharmaceutically-acceptable as    excipients as well, for injection. A particularly important example    of a succinct class of compounds where a Drug Master File (DMF) is    on file is the class of Pluronic (Poloxamer) surfactants, for which    BASF has a DMF on file. In this case, although only a few members of    this class have explicitly been used in injectable formulations, for    the purposes of this invention, the homogeneity of the class, the    presence of a DMF, and the existence of approved-for-injection    formulations using several members of the class is sufficient to    include each of the members of the class of Pluronics as    pharmaceutically-acceptable for injectable products.-   Stabilized particle. For the purposes of this disclosure, for    brevity the term “stabilized particle” will mean a particle that    can, in plurality, form a stable dispersion in a liquid, preferably    a liquid comprising a polar solvent, and most preferably comprising    water or glycerol. A stable dispersion means that the particle    dispersion does not show detrimental effects from flocculation or    fusion over time scales of at least several days, preferably several    weeks and most preferably over several months.-   Target, target cell: In some cases these terms will have slightly    different meanings in this disclosure as often used in the art. By    “target” we mean the cell, or other moiety, to which the active must    be delivered by the particle in order to be absorbed or otherwise    made available—whether or not that corresponds to the ultimate site    of action of the active. For example, if a drug is delivered    perorally within particles of the invention, the target would    typically be an absorptive intestinal epithelial cell, no matter    what the site of action of the drug after systemic absorption. If    the particle accomplishes the task of getting the active absorbed at    the target site, then it has been successful in its pharmaceutical    task.-   Targeting moiety, targeting compound: In this disclosure, this term    will have a meaning that is quite distinct from that of “target” or    “target cell” as defined above. A targeting moiety is a chemical    group that is part of the particle of the instant invention,    situated either inside the liquid crystal or bound to the surface of    the particle, and serves as a molecular target for some compound    outside the particle in the application, typically though not always    a biomolecule in the body of a mammal. A targeting compound, then,    is a compound that contains a targeting moiety. It is important to    point out that the targeting moiety is incorporated in the current    invention without the introduction of another phase at the surface    of the particle. In other words, as discussed elsewhere herein, the    number of thermodynamic phases is not increased. An example of a    targeting moiety would be an antibody that is attached to the    particle, for example by a covalent bonding to a flexible spacer    that is lipid-anchored into the particle, such that the antibody    contains a targeting moiety that will bind to a biological molecule    (the antigen) in the body and thus locate the particle at the    desired site of action. In this case, the targeting moiety may be    thought of as either a binding motif on the antibody, or the entire    antibody itself.-   Dissolution: By the term “dissolution” is meant that a compound    under consideration is dissolving, or is “undergoing dissolution”.-   Solubilize: This term is meant to be essentially synonymous with the    term “dissolve” or “dissolution”, though with a different    connotation. A compound under consideration is solubilized in a    liquid or liquid crystalline material if and only if the molecules    of the compound are able to diffuse within the liquid or liquid    crystalline material as individual molecules, and that such material    with the compound in it make up a single thermodynamic phase. It    should be borne in mind that slightly different connotations are    associated with the terms “dissolve” and “solubilize”. Typically the    term “dissolve” is used to describe the simple act of putting a    crystalline compound in a liquid or liquid crystalline material and    allowing or encouraging that compound to break up and dissolve in    the material, whereas the terms “solubilize” and “solubilization”    generally refer to a concerted effort to find an appropriate liquid    or liquid crystalline material that is capable of dissolving such    compound.-   Chemical criteria: A number of criteria have been tabulated and    discussed in detail by Robert Laughlin for determining whether a    given polar group is functional as a surfactant head group, where    the definition of surfactant includes the formation in water of    nanostructured phases even at rather low concentrations. R.    Laughlin, Advances in Liquid Crystals, pp. 3-41, 1978. A further    discussion and listings of topics including: polar groups which are    not operative as surfactant head groups; polar groups which are    operative as surfactant head groups; apolar group; and    single-component block copolymers; see U.S. Pat. No. 6,638,621, the    complete contents of which is hereby incorporated by reference.-   Reversed liquid crystalline phases, including reversed hexagonal    phase and reversed cubic phase (the latter of which includes both    reversed bicontinuous cubic phase and reversed discrete cubic phase)    are understood to be as described in detail elsewhere (e.g. in U.S.    Pat. No. 6,638.621, the complete contents of which is herein    incorporated by reference). These phases are known in the art of    surfactant self-association.

Methods and Materials

In this invention, the process typically begins with the selection of aliquid crystal composition that preferably solubilizes, or otherwiseentraps (e.g., incorporates) the active, and has the appropriatephysicochemical characteristics for the desired interactions asdescribed herein. An active may be described as “entrapped” by theliquid crystal composition if, for example, the active is solubilized inan oil droplet that is ultimately located within the particle, or if theactive is in crystalline form, and the crystals are ultimately dispersedthroughout the particle. Compositions for reversed liquid crystallinephases are discussed at length in U.S. Pat. No. 6,482,517 the contentsof which are incorporated herein by reference, and in U.S. patentapplication Ser. Nos. 09/994,937 and 10/460,659, which are hereinincorporated by,reference. As will be discussed in greater detail below,in the most preferred form, the active forms a component of the reversedcubic or reversed hexagonal phase.

An important consideration in the selection of a liquid crystalcomposition, which may not be obvious to those schooled in thetraditional art, is that the composition chosen for the liquid crystalmust be robust enough—in particular, must have a high enough meltingpoint, the best single measure of this characteristic—that it canaccommodate the incorporation of a charged, bilayer-associated componentsuch as an ionic surfactant. Such components often (though notuniversally) have the effect of melting materials such as reversed cubicphases. When a reversed cubic phase melts, e.g., by the addition of acharged bilayer-associated component, it will usually melt into eitheran L2 phase, or an L3 phase, both of which suffer from limitedinteractions with biological barriers, as described herein.

Exceptions to the general rule that high loadings (greater than about8%, or especially greater than 15%) of a charged surfactant usually meltthe reversed liquid crystalline phases most often occur when thesurfactant has two (or more) long hydrophobic chains (greater than orequal to 12 carbons each) and a polar head group of relatively low MW,in particular MW<300, particularly if the hydrophobic chains aresaturated alkane chains. Thus, a double-chained surfactant such asdidodecyldimethylammonium bromide will not typically cause the meltingof a reversed liquid crystalline phase material, nor will a chargedphospholipid molecule particularly if it is saturated. Thosedouble-chained phospholipids which are sufficiently strongly charged forthis application include phosphatidylglycerol, phosphatidylserine,phosphatidylinositol, and phosphatidic acid, but not phosphatidylcholineor phosphatidylethanolamine.

After, or concomitantly with, the selection of liquid crystalcomposition, one or more appropriate ionically-charged,bilayer-associated components is/are selected based on such propertiesas partition coefficient (generally high is best, preferably greaterthan about 1,000), low toxicity, favorable regulatory status (dependenton the route of administration), and solubility and compatibility withthe other components of the formulation. A selection of such componentsis given herein.

In the course of this work it was established that once the zetapotential of a collection of these reversed liquid crystalline phaseparticles equals or exceeds about 25 millivolts in magnitude (that is,more positive than 25 mV or more negative than −25 or preferably greaterthan about 30 mV in magnitude (or more negative than −30 mV), then noother mechanism is required for stabilization of the dispersion againstflocculation. In some cases, other exceptional attractive forces, suchas intermingling of surface-associated polymer chains, unusual ionicconditions, time-dependent redistributions within the particles, mayprevent the formation of stabilized particles by this method alone.

It is generally agreed in the art that differences in zeta potentialsare not significant unless they differ by approximately 5 mV or more.Phrased otherwise, with little loss of information, zeta potentials canbe reported as multiples of 5 mV. Thus, the rule that 30 mV (positive ornegative) or greater is sufficient for charge-stabilization will bephrased, for the purposes of this disclosure, as the criterion that azeta potential greater than about 25 mV in magnitude is what theinvention calls for as a surface charge, with a value greater than about30 mV being especially preferred.

It is important to optimize the ratio of charged surfactant to liquidcrystal, when charge-stabilizing liquid crystalline particles forinjection. Eliminating or minimizing particle populations that lie belowthe critical zeta potential required for stabilization is important forstability and sets a minimum value for the ratio, and this isillustrated in the Examples below with quantitative measurements, as perthe preferred method. It is preferred that the intensity-weightedfraction of particles with zeta potential less than 25 mV in magnitudebe less than about 10%, and more preferably less than about 3%. Notethat this refers to the intensity-weighted distribution as determined bya light-scattering method, and in cases where, say, 10% of the reporteddistribution lies below 25 mV in magnitude, it must be remembered thatdiffusional broadening exaggerates this reported value, and so theactual intensity-weighted population at values below 30 mV will in factbe considerably less than this.

These zeta potential requirements should be met without utilizing undueconcentrations of charged surfactant. One reason for this is that theintroduction of larger loadings of charged surfactant may lead to anincrease in toxicity of the formulation. While ionic surfactants such asSDS, docusate, and benzalkonium chloride (a well known preservative) arecurrently present in FDA-approved injectable formulations, this is notto say that they are void of toxic effects at even larger doses,particularly in the case of cationic compounds. FDA policies generallyrecommend the use of the least amount of excipient required for the job,in this case for stabilization.

The use of surfactants with polymeric hydrophilic polar groups,particularly polyethyleneglycol (PEG), such as Pluronics (Poloxamers) orPEGylated sorbitol or glycerol esters, with HLB values greater thanabout 8 or total PEG molecular weight greater than about 2,000 should beminimized in the practice of this invention since they, like excessiveratios of charged surfactant to cubic phase, have a strong tendency toinduce L3 or lamellar phase coatings. Such surfactants are also known toexhibit a “stacking effect” on surfaces; quasielastic light scatteringmeasurements on particles dispersed with high-HLB Pluronics, forexample, show an increase in particle diameter as the concentration ofthe high-HLB Pluronic increases, indicating the stacking of surfactantmolecules at the particle surface, which will clearly interfere withparticle-cell interactions as discussed herein.

Incorporation of active. There are three general forms in which activecan be incorporated in the uncoated particle of the instant invention.These are now described.

First form: In this form—the preferred form—the active is dissolved inthe reversed liquid crystalline phase material. Phrased more precisely,the active is one of the components which, together with the othercomponents, form the liquid crystal under the conditions used(temperature, pressure, etc.), as a thermodynamic equilibrium phase.Note that this is not necessarily the same as saying that the active is“added to” the reversed liquid crystalline phase, because the phase towhich the active is added could be entirely different before theaddition of the active; addition of the active may promote formation ofthe reversed liquid crystalline phase. For example, in Examples givenherein involving propofol the active propofol is solubilized in theliquid crystal as a “first form” i.e. the propofol is solubilized in thereversed liquid crystalline phase material, and is one of the componentsthat form the liquid crystalline material.

Second form: In this form, the active is dispersed in the reversedliquid crystalline phase material, in the form of either crystals, whichare preferably submicron, or an amorphous solid form. In this case, bydefinition, the portion of active that is dispersed, and not dissolved,does not affect the phase behavior of the liquid crystalline material.This type of embodiment can be realized in at least three ways. In thepreferred method, the active is physically mixed with the reversedliquid crystalline phase material, and the resulting material is thendispersed in water as disclosed elsewhere herein. Prior to mixing, theactive may be subjected to micronization, or even made submicron. Ifthis requires the use of surfactant or other stabilizer, then it must bechecked that this stabilizer will not disrupt the reversed liquidcrystalline phase, at the levels used. Methods for producing submicroncrystals of drug material in a pharmaceutically-acceptable manner havebeen described, for example in the U.S. Pat. No. 5,510,118 cited above.In a second method of this form, solid active particles are dispersedalong with the reversed liquid crystalline phase, with the intentionthat the liquid crystal will cover the solid active due to a lowerinterfacial tension, a more favorable sum of interactions between thesolid active and liquid crystal, and liquid crystal and polar liquidcontinuous phase. In the third method, the active is first solubilized,either in the liquid, preferably a polar solvent, or, preferably, in theliquid crystal or a precursor thereof, at, for example, elevatedtemperature or a favorable pH, and then conditions are changed toprecipitate or crystallize the active, preferably in the interior of theliquid crystalline matrix.

Third form: the active is in liquid form, either as a liquid active (forexample, in the case of a liquid drug) or as a solution of drug in aliquid phase that is (necessarily) distinct from and interior to theliquid crystalline phase material. This liquid is embedded in the liquidcrystalline material, surrounded by a contiguous and continuous matrixof the liquid crystalline material.

Combinations of these three forms are possible. For example, a portionof the active could be solubilized in the liquid crystal, whereas theremainder might be in crystalline fore dispersed in the liquid crystal.

In the First Form as just described, where the active is dissolved inthe reversed cubic or reversed hexagonal liquid crystalline phase, it ishighly desirable that in the final dispersion, the majority of theactive is localized in the liquid crystalline phase, that is in theparticles, as opposed to in the aqueous exterior. In this way, the useof the invention can take full advantage of the features of the reversedliquid crystalline phase as described herein: the sequestration andprotection of the drug both in storage and against attack frombiological components of the body; the intimate interactions between theparticles and biological membranes; any targeting capabilities builtinto the particles such as antibodies or lectins; any antioxidant (e.g.,tocopherol) or otherwise protective components in the particles;favorable and more physiological conformation and presentation ofbioactive compounds especially proteins; biomimetic nature of thevehicle as relate to biomembranes, etc. Furthermore, as discussedherein, a number of drugs are believed to exhibit a harmful effect(e.g., stinging on injection) when present, even in tiny amounts, in theaqueous exterior phase of a microdroplet or microparticulate system, yetnot when localized inside a hydrophobic particle or droplet. It is infact generally preferred in these embodiments that over about 90% of thedrug be preferentially located in the particles, and—as seen in Example18 and the discussion surrounding it—especially preferred if over about99% of the drug is preferentially located in the particles (see Example18), particularly in the case where the drug is propofol.

In the Third Form, where the active is a liquid embedded in the liquidcrystalline material, surrounded by a contiguous and continuous matrixof the liquid crystalline material, one can reasonably expect that thedrug will remain associated with the liquid crystalline material in thebody and so reap the advantages of the association. This should becontrasted with U.S. Pat. No. 6,071,524 in which cubic gel particles aresituated at the interface between oil microdroplets and the aqueousexterior phase. With the huge surface area of oil-water interfaces inthe body, and this topologically weak spatial relationship between thegel particles and the oil droplets, there is good reason to believe (andno evidence given to the contrary in U.S. Pat. No. 6,071,524) that thegel particles will be stripped from the oil droplets in their coursethrough the body, in a pharmaceutical application of U.S. Pat. No.6,071,524. Nor is there compelling reason to believe that the oildroplets will be transported across a biomembrane barrier even lithecubic gel particles themselves are.

Incorporation of a charged, bilayer-associated component. A key aspectof the invention is the incorporation of an ionically-charged,bilayer-associated compound that induces a charge throughout thebilayer, and creates a surface charge on particles of the liquidcrystalline material. There are two general methods for incorporatingthis charged compound, although the net result is typically not affectedby the choice of method. In one method, the charged compound is mixedtogether with the liquid crystalline material—or in some cases, thereversed liquid crystalline phase requires the presence of the chargedcompound. In another method, the charged compound is present in theliquid phase, preferably solubilized therein, and the liquid crystal isdispersed in this mixture. In the end, the components will tend towardequilibration, which will tend to minimize the difference between theseapproaches, such that the charged component will partition between theliquid crystalline particles and the polar phase according to adistribution that eventually would come to an equilibrium, ornear-equilibrium, distribution.

The charged, bilayer-associated compound will often, though not always,he a charged surfactant, either an anionic surfactant or, more rarely, acationic surfactant. Examples of such surfactants,pharmaceutically-acceptable for various routes of administration, aregiven below. In many embodiments of the invention, however, the chargedcompound will not satisfy the definition (given above) of a surfactant,but will nonetheless be perfectly well suited as a charged,bilayer-associated compound capable of yielding particles of the instantinvention. The charged bilayer associated compound may be the active.

Anionic bilayer-associated compounds. For formulations intended foradministration by injection or other non-oral routes, especiallypreferred anionic moieties for binding the drug are: docusate,dodecylsulfate, deoxycholic acid (and related cholates, such asglycocholate), tocopherol succinate, stearic acid and other 18-carbonfatty acids including oleic, linoleic, and linolenic acids, gentisicacid, hydrophobic amino acids including tryptophan, tyrosine, leucine,isoleucine, aspartic acid, cystine, and their N-methylated derivatives,particularly N-acetyltryptophan, myristyl gamma-picolinium chloride,phosphatidylserine, phosphatidylinositol, phosphatidylglycerol(particularly dimyristoyl phosphatidylglycerol), and other anionic andacidic phospholipids. The person with skill in the art will recognizedocusate as the anionic moiety of the surfactant docusate sodium (alsoknown as Aerosol OT), and dodecylsulfate as the anionic moiety of thesurfactant sodium dodecylsulfate, or SOS. Surface-active polypeptidesand proteins, such as casein and albumin, may also be used, althoughcareful attention must be paid to the pH which will have an effect onthe charge of the molecule.

For formulations intended for oral administration, the above anioniccompounds can be used, but in addition there are a number of othercompounds that can provide the anion. These include ascorbyl palmitate,stearoyl lactylate, glycyrrhizin, monoglyceride citrate, stearylcitrate, sodium stearyl fumarate, JBR-99 rhamnolipid (and otherbiosurfactants from Jeneil Biosurfactant), glycocholic acid, taurocholicacid, and taurochenodeoxycholic acid.

Especially preferred anionic surfactants are: sodium oleate, sodiumdodecyl sulfate, sodium diethylhexyl sulfosuccinate, sodiumdimethylhexyl sulfosuccinate, sodium di-2-ethylacetate, sodium2-ethylhexyl sulfate, sodium undecane-3-sulfate, sodiumethylphenylundecanoate, carboxylate soaps of the form IC_(n), where thechain length n is between 8 and 20 and I is a monovalent counterion suchas sodium, potassium, ammonium, etc.

Cationic bilayer-associated compounds. As discussed herein, currentlythe selection of pharmaceutically-acceptable cationic surfactants forinjection is primarily limited to myristyl-gamma-picolinium chloride andbenzalkonium chloride. However, a number of other cationic lipids andsurfactants are currently under investigation as pharmaceuticalexcipients for injectables, including: tocopheryl dimethylaminoacetatehydrochloride, Cytofectin gs,1,2-dioleoyl-sn-glycero-3-trimethylammonium-propane, cholesterol linkedto lysinamide or ornithinamide, dimethyldioctadecyl ammonium bromide,1,2-dioleoyl-sn-3-ethylphosphocholine and other double-chained lipidswith a cationic charge carried by a phosphorus or arsenic atom,trimethyl aminoethane carbamoyl cholesterol iodide,O,O′-ditetradecanoyl-N-(alpha-trimethyl ammonioacetyl) diethanolaminechloride (DC-6-14),N-[(1-(2,3-dioleyloxy)propyl)]-N-N-N-trimethylammonium chloride,N-methyl-4-(dioleyl)methylpyridinium chloride (“saint-2”), lipidicglycosides with amino alkyl pendent groups,1,2-dimyristyloxypropyl-3-dimethylhydroxyethyl ammonium bromide,bis[2-(11-phenoxyundecanoate)ethyl]-dimethylammonium bromide,N-hexadecyl-N-10-[O-(4-acetoxy)-phenylundecanoate]ethyl-dimethylammoniumbromide, 3-beta-[N-(N′,N′-dimethylaminoethane)-carbamoyl.

Other useful bilayer-associated compounds. Other suitable chargedbilayer-associated compounds for use in the instant invention, which cantake up a charge under at least some conditions, include: fatty acids,phenolic compounds such as eugenol, isoeugenol, quinolines,hydroxyquinolines and benzoquinolines, tricyclics such as carbazole,phenothiazine, etc., pigments, chlorophyll, certain natural oil extractsparticularly those which are phenolic (such as clove oil, ginger oil,basil oil), biosurfactants (such as Jeneil's “JBR-99”), a wide range ofdyes. Amphiphilic proteins and polypeptides can be used, includinggramicidin, casein, albumin, glycoproteins, lipid-anchored proteins,receptor proteins and other membrane proteins such as proteinase A,amyloglucosidase, enkephalinase, dipeptidyl peptidase IV, gamma-glutamyltransferase, galactosidase, neuraminidase, alpha-mannosidase,cholinesterase, arylamidase, surfactin, ferrochelatase, spiralin,penicillin-binding proteins, microsomal glycotransferases, kinases,bacterial outer membrane proteins, and histocompatibility antigens. Asis well known, every protein has a net charge except at its isoelectricpoint (pI), and thus a pharmaceutically-acceptable membrane-associatedprotein is suitable for use in the present invention as long as the pHis away from its isoelectric point. A few such proteins are currentlyaccepted as inactive ingredients for pharmaceutical preparations, atleast under some conditions, and these include gluten, casein, andalbumin.

Surfactants and lipids. Low-toxicity, especiallypharmaceutically-acceptable, lipids and surfactants form the basis ofthe lyotropic liquid crystalline phases that are a fundamental buildingblock of the current invention. Preferred surfactants which areFDA-approved as injectables and other low-toxicity surfactants andlipids, which are of at least relatively low solubility in water, thatare preferred for the present invention for products intended for anumber of routes of administration, include those listed in U.S. Pat.No. 6,638,621, the complete contents of which is herein incorporated byreference. The inventor has found the followingpharmaceutically-acceptable surfactants to be particularly useful informing insoluble reversed cubic and hexagonal phases:phosphatidylcholine, phosphatidylethanolamine, Arlatone G, Tween 85,glycerol monooleate and other long-chain unsaturated monoglycerides,sorbitan monooleate, zinc and calcium docusate, and Pluronics with lessthan about 30% PEO groups by weight, especially Pluronic L122 and to alesser extent L101; Pluronic P123 (and likewise Pluronic 103) also formsreversed cubic and hexagonal phases but has a significant solubility inwater which can limit its usefulness in some applications. The low-MWethoxylated surfactants OE-2 and OE-5 (oleyl alcohol ether-linked toeither 5 or 2 PEG groups) are useful in this respect but their approvalin drag formulations is limited, depending on the route ofadministration.

Polar solvent. Polar solvents are required in the present invention forthe creation of the lyotropic liquid crystalline phase material, andpreferred as a continuous phase for dispersing said material. Usually,at least in the case of a bicontinuous cubic phase, which is thepreferred embodiment, the polar solvent composition in the liquidcrystal and in the continuous (exterior) phase will ultimately be equal,or nearly equal, because the two are essentially in hydrauliccontinuity. It should also be noted that the choice of a non-volatilepolar solvent like glycerol can be important in processes such asspray-drying. The polar solvent may be: water; glycerol; formamide,N-methyl formamide, or dimethylformamide; ethylene glycol or otherpolyhydric alcohol; ethylammonium nitrate; other non-aqueous polarsolvents such as N-methyl sydnone, N-methyl acetamide,dimethylacetamide, pyridinium chloride, etc.; or a mixture of two ormore of the above, with water-glycerol being the most important of themixtures.

For the case of drug-delivery, the preferred polar solvents are water,glycerol, N,N-dimethylacetamide, and N-methylacetamide, as well asmixtures thereof. Water-glycerol mixtures are of extremely low-toxicityand are very compatible with many surfactants including phospholipids.Dimethylacetamide-glycerol mixtures are excellent for dissolvingdifficultly-soluble pharmaceutical compounds.

It can be advantageous in certain circumstances to use, as analternative form of this invention, a composition that yields acharge-stabilized dispersion of reversed liquid crystalline phaseparticles upon contact with water (or more rarely, other polar solventor liquid)—whether or not this dehydrated composition itself is areversed liquid crystalline phase (i.e., a reconstirutable material thatforms uncoated particles when combined with medium (water or some otherfluid) where the particles thus formed have an ionic charge whichstabilizes them as a solution or dispersion in a liquid (e.g., water).In particular, this contact with water or a water-containing mixturecould be either during a reconstitution step, or during the applicationof the particle, when the particle contacts an aqueous solution such asblood, extracellular fluid, intracellular fluid, mucous, intestinalfluid, etc. This can he in the form of particles, or a precursor liquid,as seen in Example 17, or a solid or semisolid matrix. There are severalreasons why this may be advantageous, including the following withoutlimitation: to protect hydrolytically unstable actives or excipients; tolimit premature release of water-soluble actives; and as a naturalresult of a production process such as spray-drying or freeze-dryingthat can induce dehydration. Removal of most, or all, of the water froma reversed liquid crystalline phase will often yield anothernanostructured liquid or liquid crystalline phase, but can sometimesyield a structureless solution, precipitate, or a mixture of these withone or more nanostructured liquid or liquid crystalline phases. In anycase, for many applications, it is the hydrated form that is importantin the application of the particles, and thus if this hydrated form is areversed liquid crystalline phase, then the composition of matter fallswithin the scope of the current invention.

Preferred methods of making. The preferred method of practicing thecurrent invention is as follows, focusing on the case of apharmaceutical active. One can choose to employ either the reversedbicontinuous cubic phase liquid crystalline material, or lesspreferably, a reversed hexagonal phase material (less preferable bothbecause of less favorable interactions with biomembranes, and increasedrisk of toxic and/or antigenic effects). A liquid crystal containing theactive is prepared by mixing the active, a surfactant or lipid, water,and if necessary a solubilizing excipient, and mixing thoroughly suchthat the resulting material is optically isotropic and of highviscosity. Methods for locating and mixing the appropriate compositionto achieve this are given in detail in U.S. Pat. Nos. 6,482,517 and6,638,621 together with U.S. application Ser. Nos. 09/994,937 and10/460,659 the contents of which are incorporated by reference. Tosummarize, these methods involve the development of phase diagrams withthe aid of polarizing optical microscopy and small-angle x-rayscattering, the application of solubilization-aiding components that arenon-paraffinic and typically contain one or more polar groups that arenot operative as surfactants (in combination with true surfactants whichare, of course, necessary for liquid crystalline behavior), andjudicious use of techniques useful for speeding dissolution such asheating, sonication, vigorous stirring/kneading, etc. The concentrationof active should be high enough that an effective therapeutic amount (a“dose”, to generalize a term from pharmaceutics) requires no more thanabout 10 grams of liquid crystal, and more preferably no more than about2 grams. If the surfactant or lipid is not strongly charged—and thiswill typically be the case in pharmaceutical applications, especiallyinjectable formulations, because most of the FDA-approved surfactantsand lipids approved for relatively high concentration use (as needed inthe liquid crystal) are not highly charged—then a relatively smallamount of charged, bilayer-associated compound must be incorporated, andthis is preferably a charged surfactant. For the cases where thisadditive is needed (that is, where the cubic phase itself does not havea charged surfactant as its main surfactant component), the weight ratioof the charged, bilayer-associated compound to the liquid crystal shouldbe between about 0.01:1 and 0.15:1, or more preferably between about0.02:1 and 0.08:1. Weight ratios larger than 0.08:1, and especiallyratios larger than 0.15:1, will have a tendency to induce an L3 phase orlamellar phase that can become an interfering coating. Ratios lower than0.01:1 will not yield sufficient surface potential to stabilize theparticles in dispersion. Although the preferred method of incorporatinga charged surfactant additive—provided it is water-soluble—is bydissolving it in the water that is used to disperse the cubic phase, itshould first be checked that the cubic phase is not melted by theaddition of small amounts of the surfactant.

The cubic phase is then dispersed in the surfactant solution, or in theother case the charged cubic phase is dispersed in water or some sort ofbuffer/aqueous solution, using homogenization or other mechanical means,preferably followed by microfluidization. In the production of particlesof this invention and their size-reduction, a number of emulsificationmethods could be used as energy inputs. These include sonication,microfluidization, valve homogenization, blade stirring, etc. Whensubmicron particles are required (e.g., in intravenous applications),microfluidization is the preferred method since the shear rates andtemperature spikes can be best controlled in that method. Filtration orextrusion, in combination with these methods, can be of great help inreducing particle size, and can serve a sterilization purpose at thesame time. Homogenization of the particle size down to a few micronsfollowed by filtration at 0.45 or 0.2 microns is another preferred meansof producing fine particles of this invention. In cases where thestiffness of the reversed liquid crystal interferes with filtration, itcan help to raise the temperature so as to perform the filtration at atemperature where the liquid crystal melts into a liquid phase(typically L2, L3 or microemulsion phase), making the sizing byfiltration easier, and then reducing the temperature back to ambient toreturn the particles to the liquid crystalline form.

Sterilization of the finished product can be either by filtration,preferably at 0.2 microns, or by other methods known in the art, such asUV or pulsed UV light, gamma irradiation, e-beam sterilization, steamsterilization, or when possible by terminal heat sterilization. Sincemany of the components used in the practice of this invention will beliquids at or near ambient temperature (e.g., many of the Pluronics,tocopherol, essential oils, aqueous solutions, and L2 phases that resultfrom mixing cubic phase compositions minus water or other liquidcomponent), there is also the possibility of starting with sterilizedliquid components (e.g., by sterile filtration) and processing understerile conditions.

Supercritical fluids can also provide other means by which to make theinvention, with supercritical carbon dioxide being the preferredsolvent. Methods that apply sonication and other high-frequency energyto compositions dissolved in supercritical carbon dioxide, with thecarbon dioxide coming off as a gas leaving microparticles, can be used.

Validation and quantification of charge stabilization. In the context ofthe instant invention, measurement of surface charge, preferably in theform of particle zeta potential, is crucial to validating that particlesof the invention are indeed present, predicting long-term stabilitycharacteristics, and to quantifying the electrostatic repulsion. Inparticular, as discussed above, in the course of this work it wasestablished that once the zeta potential of a collection of thesereversed liquid crystalline phase particles equals or exceeds about 25mV, or more preferably 30 millivolts, in magnitude (or is less than−25mV or −30mV in magnitude), then no other mechanism is required forstabilization of the dispersion against flocculation, provided thatthere are no exceptional attractive forces, such as intermingling ofsurface-associated polymer chains, unusual ionic conditions,time-dependent redistributions within the particles, etc.

In the present art, historical microscopy-based estimates ofelectrophoretic mobilities have been largely replaced by morequantitative light-scattering methods. This is not to say thatmicrosopy-based methods are useless, but in the present context, withthe focus on submicron and even nanoscale microparticles,light-scattering methods are far better suited. This is notwithstandingthe fact that for systems containing larger particles, such assubcutaneous formulations, microscopy-based determinations usingelectrophoretic observation cells can be very useful and yield moredirect, intuitive information, and such methods can even extend down tosubmicron particles particularly with specialized optics such asDifferential Interference Contrast (DIC, also known as Nomarski optics).In any case, The DELSA 440SX measurements reported herein have beencrucial to optimizing the compositions used in the present invention,particularly the ratio of charged surfactant to liquid crystal, andespecially in the task of eliminating or minimizing particle populationsthat lie below the critical zeta potential required for stabilizationwithout utilizing undue concentrations of charged surfactant.

In the Examples given herein, the conditions/settings typically appliedwere representative of the preferred procedure for determining zetapotential. The samples were loaded into a silver-coated sample cell,undiluted or only mildly diluted, which is important because dilutioncan affect zeta potentials by a number of effects. Conductivities weretypically on the order of 0.1 mS/cm, and the current in milliamps wasset to a value somewhat larger than half the value of the conductivityin mS/cm; for example, in one Example, the conductivity was 0.311 mS/cmand the current was set to 0.2 mA. The frequency shift was first set to500 Hz, and if the measurement indicated that a setting of 250 Hz wouldbe acceptable then a second measurement was taken at 250 Hz. At thelatter frequency shift, instrumental broadening was often considerablyreduced compare to the 500 Hz reading; however, particularly at thehigher angles of measurement, the peak shape could appear to have a tailat the higher zeta magnitude end, due to the so-called “homodyne”effect.

This instrument measures zeta potential at up to four anglessimultaneously: 8.9, 17.6, 26.3 and 35.2 degrees. As is well known inthe art of light-scattering, smaller angles emphasize larger particles,and vice versa. This means that at the larger angles, since smallerparticles are emphasized more, diffusional broadening is morepronounced.

The presence of a sharp peak at an indicated zeta potential of zero, inthe present context at least, is nearly always due to material that iseither stuck to the walls of the cell, or settled to the bottom. In theExamples of the present disclosure, this has much more to do with theparticle size than any other parameter, except for the fact thatcationic particles have a slightly larger tendency to stick to quartz(the material of the DELSA sample cell) due to an interaction with theweak anionic charge of quartz at the pH values investigated herein.

The simultaneous measurement at different angles is also important invalidating the measurement. In short, since this measurement (as withnearly any scientific or engineering measurement) has noise associated,the question of whether or not a given peak or feature is real orartefact can be made easier and more substantial by checking whether ornot the peak or feature is present in only one curve, or several (andpreferably all) curves corresponding to the different angles ofmeasurement.

Dry or Reconstitutable Systems

Dry, partially dry, reconstitutable and other materials that form orrevert to particles of the type disclosed herein are within the spiritand scope of the present invention. Such systems can be prepared by anumber of methods. For one, they may be obtained by freeze-drying liquidcrystalline particles, or drying such particles by other means involvingvacuum and/or heat input. Spray-drying, fluid-bed dryers and similartechniques can also be applied to either aqueous dispersions ofparticles, or to precursor solutions of the nonaqueous components of theparticles dissolved in a volatile organic solvent. All of the threeforms of the invention discussed above can be dehydrated by at leastsome of these means to produce reconstitutable systems.

This approach is especially useful when one can take advantage of thefact that many reversed lyotropic liquid crystals become solids uponremoval of their water. Examples of surfactants and lipids that formreversed liquid crystalline phases upon hydration but are (effectively)solid in dried form are monoelaidin, sodium docusate (and other salts ofdocusate), certain phospholipids depending on acyl chain unsaturation,and mixtures of didodecyldimethylammonium bromide with tetradecanol.

Alternatively, drying a dispersion can produce a reconstitutable systemof several sorts. If there are relatively small amounts of non-volatilecomponents in the exterior phase of the dispersion, then drying willleave either a fused mass—essentially the original contiguous liquidcrystal—or a collection of distinct particles that can, at least inprinciple, be redispersed with a relatively low input of energy. Thelatter scenario can be promoted by selection of a higher melting pointsurfactant or other component.

By incorporating a non-volatile additive in the exterior phase,preferably dissolved but alternatively dispersed, drying can result inparticles that are kept from liquid crystal-liquid crystal fusion by thepresence of an intervening solid. Selecting an additive that isoppositely-charged from the liquid crystalline particles can aid inestablishing the proper localization of the resulting solid. Since thesolid is either soluble, or readily dispersible, in the original liquid(usually water), then addition of this liquid will generally result inprompt reconstitution of a dispersion. Particle size of thereconstituted dispersion may be the same as that of the originaldispersion, but in the event it is larger, then simple methods asdescribed herein can be used to reduce the particle size; in particular,in many cases a filtration or extrusion step will induce the desiredparticle size while sterilizing as well, and a syringe filtration stepis a well-accepted procedure even in the case of a bedsidereconstitution.

Reversed Liquid Crystalline Phase Induction

In some instances, the active of interest is such that it induces areversed liquid crystalline phase in a selected lamellar-forminglipid-water or surfactant-water system. As a particularly important andpreferred ease of this, the lipid-water system is a phospholipid-watersystem, especially a phosphatidylcholine-water system in which thephospholipid is sufficiently unsaturated to form a lamellar liquidcrystalline system at or near ambient temperature. Phosphatidylcholinepurified from most plant sources, as well as a number of synthetic PC'swith unsaturated chains, are well known to form lamellar liquidcrystalline phases at room temperature. However, it is much less wellknown that the addition of certain hydrophobic or amphiphilic compoundscan induce the lamellar phase to convert to a reversed cubic, or lesscommonly reversed hexagonal, phase. Many solubilizing oils, such as anumber of essential oils (indeed, the majority of these), inducereversed cubic phases, typically at levels between about 10 and 35% ofthe final composition. Certain actives, including pharmaceutical activessuch as propofol, also induce cubic phases in phosphatidylcholine-watersystems, as the current inventor has found. These surprising cases,where the drug—or a drug/diluent combination, such as a mixture ofpropofol and tocopherol—is found to induce a reversed liquid crystallinephase in an otherwise lamellar-forming surfactant-water mixture, areespecially well-suited for this invention. This is illustrated by thelarge loadings (29% by wt.) that are achievable in the PC-propofol-watercubic phase in the Examples shown below, which resulted in low levels ofexcipients being delivered in the course of treating a mammal with theformulation.

Applying the Invention.

The uncoated particles of the present invention have application in avariety of fields. The particles may be adapted to absorb one or morematerials from a selected environment, adsorb one or more materials froma selected environment or, most preferably, to release one or morematerials, such as active agents, into a selected environment.

With respect to absorption, the particles may be used, for example, toharvest products or scavenge waste in biological or chemical reactionprocesses; or to remove toxins, antigens or waste products in medicalapplications.

With respect to adsorption, for example, the particles may be used aschromatographic media and as adsorbents. In applications where theactive agent is a target molecule that is capable of capturing ananalyte, such as a biologically or chemically important molecule orother compound from the surrounding medium, the uncoated particles ofthis invention have an advantage over coated particles of any sort inthat the liquid crystal is presented directly to the medium with theleast amount of interference.

With respect to release, the particles may be used for the controlledrelease of pharmaceutical agents such as anticancer agents orphotodynamic therapy agents, local and general anesthetic agents,anesthetic reversal agents, or cosmetic, nutritional, nutriceutical, orcosmeceutical materials. An active agent may be located within theparticles for release upon the triggering of release.

One very valuable aspect of the invention applies in particular tohighly insoluble actives, insoluble drugs in particular. A major focusin drug development is the water solubility of drug candidates, andconsiderable resources are spent measuring, optimizing, and evaluatingthis solubility, even in cases where it is very low. The prevalentconception is, in fact, that this is a crucial parameter because, atsome point in the path to absorption, the drug will have to dissolve inwater en route to the target cell membrane. However, it is recognized inthis invention that uncoated particles as disclosed herein, whichinteract intimately with target membranes, can greatly reduce or evencircumvent the need for diffusion of “naked” drug (drug that is nolonger in the particle core) across aqueous paths to reach the targetmembrane—aqueous paths which themselves represent barriers, effectively.Indeed, it is envisioned that from the moment a drug molecule isdissolved in a particle of the present invention, to the point it islocated in the target cell membrane, it need never cross over an aqueouspath; the particle can incorporate the active as a component up to thetarget cell, at which point the reversed liquid crystalline phase canfuse and integrate with the target cell membrane, depositing the drugdirectly into the cell membrane.

Proteins, polypeptides, nucleic acids, polysaccharides, lectins,antibodies, receptors and other biomacromolecules are actives that canbe particularly well suited for the current invention. The reversedliquid crystalline phase can provide the absorption enhancementproperties discussed herein—which can be especially important in thecase of macromolecules—while at the same time providing protectionagainst degrading proteins (proteases, nucleases, glycosidases,antibodies, etc.) and cells that would otherwise inactive or sequesterthe active; such protection can in fact be provided by the effect of thecontrolled pore size of the reversed liquid crystalline phases, or byvirtue of the lack of accessible pores in the discrete(non-bicontinuous) cubic phase though this phase is less effective thanthe bicontinuous cubic phase at enhancing transport. The uniformporesize in the reversed bicontinuous cubic phase and the reversedhexagonal phase can likely be utilized to release a large molecule inresponse to a physiological or other condition (e.g., temperature orhydration, in a laundry detergent application) that induces amicrostructure with poresize large enough to release the macromolecule.As with small molecules, release of the active can also be triggered bychanges in ionic conditions, such as a change in pH, salinity, divalention concentration, hydrogen bonding species, or even cleavage of bondsbetween the active and a component of the liquid crystal by eitherchemical or biochemical (e.g., enzymatic) action. In some cases, it willnot be necessary to release the active, if it is a reactive or catalyticcompound, particularly a protein, provided the substrate or otherreactant(s) is able to pass through the pores of the reversed liquidcrystalline phase material. In the case of nucleic acids in particular,but also in other cases, particles of the current invention could be ofgreat utility in delivering actives to intracellular sites, such as thenucleus or nuclear membrane, the Golgi apparatus, the endoplasmicreticulum, the mitochondria, etc., and in such a case thetransport-enhancing properties of the reversed liquid crystalline phasematerials, particularly the reversed bicontinuous cubic phases, can beof high utility in the context of an uncoated particle.

In cases of pharmaceutical application of the invention where the drugis disposed in the particle in crystalline form (as opposed tosolubilized), within a reversed liquid crystalline microparticle, andthus surrounded by a contiguous and continuous matrix of the liquidcrystalline material, and particularly when the particles are alsosubmicron in size, then the reversed liquid crystalline material portionof the particle can serve a number of functions simultaneously,including but not limited to: stabilizing the particles in dispersion;enhancing absorption by improving interactions with biomembranes andother barriers; serving as a matrix for the solubilization of otherexcipients or co-factors; serving as a matrix for the solubilization ofefflux protein inhibitors in particular; providing a means by which tomodulate, and even reverse, the effective charge on the drug; provideimproved compatibility with certain drug formulation approaches; providefor modulation of the deposition characteristics of drugs by thepresence of a bioadhesive and/or high-viscosity matrix; provide forporesize-selective protection from, or access of, biomacromolecules(e.g., albumin, proteases, nucleases, esterases) to the solid drug; inthe case of a prodrug, provide for drug targeting or controlled releasedelivery by permselective access and/or controlled dissolution of thematrix; and provide for improved stabilization of the drug dispersion inbiological fluids by the use of liquid crystals that have much lowersolubilities than most of the surfactants previously used in nanocrystalstabilization.

One particularly important potential application of the invention is forhosting molecules, such as antibodies, receptors, ligands, nucleicacids, oligosaccharides, or other compounds that can bind an analytemolecule in a diagnostic situation. In a preferred embodiment of such anapplication, a target compound capable of binding a chemical of interestis partitioned into a particle of the current invention. In acompetitive assay or simple segregation application of the invention,the chemical of interest will diffuse into the porous reversed liquidcrystalline particle and bind to the target. In competitive assays, adisplaceable chemical such as an enzyme group or the like will bedisplaced by the chemical of interest and will diffuse out of the porousreversed liquid crystalline particle and react with a marker compound toindicate binding has occurred within the particle; see in particularU.S. application Ser. No. 10/170,214. Thus, the nanostructured liquidcrystalline particle keeps the enzyme or other displaceable groupsseparate from the marker compound until it is released from the target,thereby allowing accurate detection without complex washing, aspirationand other processes used in many equipment-intensive automatedimmunoassay analyzers. This allows clinicians to conduct tests quicklyand accurately, without sophisticated training or instrumentation. In asandwich assay application of the invention, a ligand is bound to thetarget within the porous reversed liquid crystalline particle, or canbecome bound to the target by diffusion through the porous liquidcrystalline material. In addition, a second target that can diffusethrough the reversed liquid crystalline material is added which binds toanother epitope of the ligand. Once the second target is bound, anindication is provided demonstrating the binding. In such applicationswherein the target must bind a molecule from a milieu of interest, againthe presence of a coating is intrusive, even a porous L3 phase becauseof its tendency (described above) to form lamellar phase domains, whichcan be of very low permeability to a wide range of compounds. Indeed,this is the reason why nature uses bilayers to compartmentalize cells.

Alternative uses of the invention arc in chemical isolation and cleanup, or in the delivery of enzymes, or other bioactive agent, e.g.,radioactive agents and chemical toxins. In the chemical isolationapplication, the particles of the present invention are brought intocontact with a medium in which segregation and isolation of a chemicalof interest is desired. Over a period of time, and with or withoutoperations such as stirring, agitation, etc., the chemical diffuseswithin the porous reversed liquid crystalline particle and is bound bythe target. This process may be used in the clean up of contaminatedwater, or in the ex vivo clean up of blood, for example. In the deliverymode, the porous liquid crystalline particle would incorporate achemical to be delivered (e.g., an agonist, antagonist, medicament,toxin, etc.). This chemical would be protected from the environment,e.g., the body in an in vivo application, by the porous liquidcrystalline particle, until it is in position for delivery of thechemical. Once in position, a compound from the environment will diffusethrough the porous liquid crystalline particle, competitively interactwith the target and displace the chemical to be delivered, and,thereafter, the chemical to be delivered will diffuse out of the porousreversed liquid crystalline particle and into the environment in whichit should act.

Various other applications of microparticles in general are known,including those listed in U.S. Pat. No. 6,638,621, the complete contentsof which are herein incorporated by reference.

In view of the demanding requirements for the delivery ofpharmaceuticals, the advantages and flexibility of the present inventionmake it particularly attractive in the delivery and release of manypharmaceutical compounds, particularly for the delivery and release oftherapeutic amounts of such substances. Pharmaceutical compounds thatare particularly well-suited for incorporation as actives in the instantinvention, and suffer from problems or limitations in thecurrently-marketed formulations, include propofol, alphaxalone,alphadolone, eltanolone, propanidid, ketamine, pregnanolone, etomidate,and other general anesthetics; bupivacaine, lidocaine, procaine,tetracaine, mepivacaine, etidocaine, oxybuprocaine, cocaine, benzocaine,pramixinine, prilocaine, proparacaine, ropivicaines, chloroprocaine,dibucaine, and related local anesthetics; SN-38 and relatedcamptothecins; paclitaxel and related taxanes; doxorubicin, idarubicin,daumorubicin and related rubicins; amphotericin B; coenzme Q10; steroidsand steroidal anti-inflammatory agents; nonsteroidal anti-inflammatories(e:g., salicylates, para-aminophenol derivatives (e.g., acetaminophen),fenomates, proprionic acid derivatives (e.g., naproxen, ibuprofen,etc.); analgesics; antipyretics; sedatives (e.g., benzodiazepines suchas diazepam); hypnotics (e.g., intravenous anesthetics andbarbiturates); opiates; cannabinoids and proteins (e.g., insulin anderythropoietin)(it being understood that a wide variety of amides andesthers may have application in the present invention). In addition,various antineoplastic agents and other pharmaceutical compounds listedin U.S. Pat. Nos. 6,638,537 and 6,638,621, the complete contents ofwhich are herein incorporated by reference

We note that the current invention is also very well suited for theincorporation of functional excipients, such as essential oils thatimprove, absorption of poorly-absorbed drugs, in some cases byinhibiting drug efflux proteins. As discussed in more detail elsewhereherein, there are a number of sites within, and at the surface of theparticles, where actives, excipients, and functional excipients can belocalized within the context of this invention.

In the area of pharmaceutics and nutriceutics, the particles of thepresent invention may be administered to a mammal (including a human),or other animal, by any of a variety of routes of administration whichare well established and well known to those of skill in the art. Theseinclude but are not limited to oral (e.g., via pills, tablets, lozenges,capsules, troches, syrups and suspensions, and the like) and non-oralroutes (e.g. parenteral, intravenous, intraperitoneal, intrathecal,intramuscular, subcutaneous, intra-arterial, rectal, intravaginal,sublingual, intraocular, transdermal, intranasal, via inhalation, in asuppository, and the like). The compositions of the present inventionare particularly suited for internal (i.e., non-topical) administration,but, in some applications may be topically provided. The presentinvention is especially useful in applications where a difficultlysoluble pharmaceutical active is to be delivered internally (i.e.,non-topical), including orally and parenterally, wherein saidformulation is to be mixed with a water continuous medium such as serum,urine, blood, mucus, saliva, extracellular fluid, etc. In particular, animportant useful aspect of many of the structured fluids of focus hereinis that they lend themselves to formulation as water continuousvehicles, typically of low viscosity.

It should be noted that, in the case of injectable formulations, thecompositions of this sort reported in U.S. Pat. Nos. 5,756,108 and6,071,524, in particular, are not applicable, because they are centeredaround the use of unsaturated monoglycerides, which are highly toxic oninjection and not approved for use in injectable formulations.Similarly, U.S. application 2002/0153509 teaches away from injectableparticles with its nearly exclusive focus on monoolein.

Incorporation of targeting groups and bioactive compounds. In thepresent invention it can be very effective to incorporate chemicals orchemical groups—often proteins or other biomacromolecules—that can beinvoked to target particles temporally and spatially, for example, totarget particles to specific sites in the body. Similarly, otherbioactive compounds incorporated on or in the particles could serveimportant functions, such as: absorption enhancers such as menthol couldbe present so as to increase permeability of absorption barriers (lipidbilayers, gap junctions) prior to or concomitant with the release ofdrug; proteins or other adsorption-modulating materials could beincorporated that would inhibit unfavorable binding of endogenousproteins such as albumin; adjuvants could be incorporated that wouldenhance the effect of vaccine components or other immune modulatingmaterials. Antibodies, steroids, hormones, oligo- or polysaccharides,nucleic acids, vitamins, immunogens, and even nanoprobes are allexamples of a wide range of materials that could be attached toparticles of the instant invention, either by solubilization orcompartmentalization in the liquid crystalline material, or by covalentbonding, ionic bonding, coordinate bonding, hydrogen bonding,adsorption, specific biochemical interactions (such as avidin-biotinbinding), or other chemical interactions with components in theparticle.

While it is not always crucial for a given application to know the exactlocalization (or more precisely, the spatial probability distribution)of a targeting moiety within or in association with a particle, this maybe an important consideration in the design of a particle-targetingmoiety combination, and the instant invention lends itself to a gooddeal of flexibility and power in this respect. Typically, targetingmoieties could be substantially localized at one or more of thefollowing sites in reference to the microparticle:

1) in the particle, i.e., dissolved or dispersed in the reversed liquidcrystalline phase interior; this locality can offer the distinctadvantage of providing a “biomimetic” milieu for the targeting moiety, amilieu which can comprise a lipid bilayer as well as hydrophilic domainseach of which can be tuned to optimize the environment; also, this isthe preferred location in the case where the microparticle is used inthe diagnostic methodology described in U.S. patent application Ser. No.10/170,214;

2) at the surface of the particle; and/or

3) attached to, but at a distance from, the surface of the particle,through attachment via a flexible spacer, e.g., a polymer that isattached (e.g. by covalently bonding) at one end to a component of theparticle and at the other end to the targeting moiety. Experience withother types of microparticles in the art has shown that this isgenerally an excellent approach for achieving good targeting because itpreserves important conformational and diffusional degrees of freedomthat are sometimes required for good docking of a targeting moiety witha receptor or target.

It is also possible in the present invention to create a responsivetargeting moiety by tuning the conditions of the formulation such thatthe targeting moiety is located preferentially in the protectiveinterior of the particle until such time as it is needed for itstargeting task, at which point local conditions such as pH or ligandconcentrations could induce the moiety to leave the interior of theparticle and present itself at, or outside of (via a spacer) theparticle surface. For example, if a targeting moiety had a net charge,say cationic, at the pH values encountered during product shelf and evenin transit to the site of action, thereby sequestering the target moietyin the interior of the particle where anionic compound(s) are present;during application, upon reaching the site of action, a change in pH,ionic strength, specific ion concentration, surfactancy, ligandconcentration or other parameter could release the targeting moiety byinterrupting the ionic binding or otherwise releasing the moiety(possibly by mass action), such that the moiety could come to theparticle surface and become available for binding to the target.Sequestration of the moiety could greatly enhance the stability of themoiety particularly in view of the small poresizes of reversed liquidcrystalline phases, which are sufficiently small to occlude the passageof certain large molecules such as proteases, nucleases, etc.

A number of compounds could potentially be used as targeting moieties ina pharmaceutical application of particles of the instant invention. Tobegin with, certain lipids, such as Lipid A, have very specificinteractions with components of the immune system, for example, and canbe incorporated into the particles. Similarly, block copolymers in whichone of the blocks could have targeting potential, such as glycogen andheparin, may be utilized. Small molecules that could be present in theparticle to achieve a degree of targeting include sterols, fatty acids,gramicidin, fragments or simulants of appropriate protein epitopes, andamino acids including aspartic acid, cysteine, tryptophan, leucine andothers.

The ability of the reversed liquid crystalline phases of the instantinvention to provide for solubilization and stabilization ofbiomolecules, such as the targeting moieties of focus here, has beendescribed above, where a number of examples of membrane proteins aregiven (receptor proteins, such proteins as proteinase A,amyloglucosidase, enkephalinase, dipeptidyl peptidase IV, gamma-glutamyltransferase, galactosidase, neuraminidase, alpha-mannosidase,cholinesterase, arylamidase, surfactin, ferrochelatase, spiralin,penicillin-binding proteins, microsomal glycotransferases, kinases,bacterial outer membrane proteins, and histocompatibility antigens),many of which could serve a targeting role if incorporated in particlesof the instant invention.

In yet another embodiment of the invention, “externally-directedtargeting” of the particles may be achieved. This may be accomplished bydirecting particles containing certain magnetically responsive materials(e.g., ferric oxide), dispersed in the particle or tethered to it,through the application of magnetic fields.

Antibodies are broadly useful for targeting to specific sites ormolecules in the body or other environments, and can be incorporated atvarious sites in a particle as discussed above. In particular, intactantibodies with their more hydrophobic Fc fragment are prone topartitioning into matrices of the type used in this invention, andfurthermore it is well known that antibodies can be adsorbed or attached(including covalently) to surfaces with retention of binding and bindingspecificity. Commercial sources supply a plethora of antibody types, forexample, those listed in U.S. Pat. No. 6,638,621, the complete contentsof which is herein incorporated by reference, and others which arecontinually under development.

Alternatively, many substances (e.g. folate, P-gp, cytochrome P450, andEGF) may in and of themselves be useful as targeting substances and maybe incorporated into the particles of the present invention.

It is important to point out that in addition to targeting compounds perse, active compounds, functional excipients such as absorptionenhancers, and other bioactive materials as gleaned from the lists ofmaterials given herein can be incorporated in any of these localizationsites.

In addition to the targeting of particles to specific sites for releaseof drug, as mentioned above particles incorporating certain radiopaqueor optically dense materials could themselves be used for imaging, andwhen coupled to targeting compounds as described herein could targetspecific sites in the body and allow their visualization. As an example,somatostatin receptors are known to be localized at certain tumor sites,so that the attachment of a target to particles as per the instantinvention that would bind selectively to somatostatin receptors couldtarget a tumor and allow visualization via, e.g., x-ray, MR imaging, orradioimaging. To extend this idea, a similarly targeted particle couldthen carry a radioactive material that would emit radiation intended toinduce necrosis of the tumor. Polymerized liquid crystals as phases.U.S. Pat. No. 5,244,799 (the contents of which are hereby incorporatedby reference in entirety) reports the polymerization of nanostructuredcubic and hexagonal phase liquid crystals, with retention of theirnanostructure. The retention of structure was demonstrated bysmall-angle x-ray scattering (SAXS) and transmission electron microscopy(TEM).

The possibility of polymerizing the cubic phase of a particle of theinstant invention opens up a number of possibilities, particularly asrelate to increasing the stability of the reversed liquid crystallinephase and modulating its interaction with the body, and cell membranesin particular. For an example of the latter, whereas an unpolymerizedcubic phase might be expected to molecularly disperse when coming intocontact with a biomembrane, polymerization might create a particle thatwould retain its integrity throughout its interaction with the samebiomembrane, and this could have dramatic consequences as to the fate ofthe particle and to a drug inside the particle. Furthermore, theretention of a bilayer-bound drug (hydrophobic small molecule, membraneprotein, etc.) might be increased tremendously by polymerization,yielding a slow-release particle. And the presence of a more permanent,precisely-defined pore structure, with precisely tunable poresize, mightmake possible improved controlled release of a drug, and/orsequestration of the drug from degradative or other enzymes bysize-exclusion from the pores of the polymerized matrix. Partitioningcontrol. In the context of this invention, it is sometimes possible toadjust the partitioning of one or more compounds, the active inparticular, into or out of the particles—so as, for example, tosignificantly reduce the levels of free drug in the exterior, aqueousphase. Examples of pharmaceutical compounds where this is importantinclude diazepam, and propofol, where the presence of propofol in theexterior phase is believed to be responsible for the burning that isexperienced by many upon injection. This is in spite of the fact that,in the case of propofol, the amount of drug which is in the aqueousphase is less that 1% of the amount of propofol that is in theparticles—that is, in the cubic phase—in all cases (see Example 18 inparticular), or, phrased otherwise, that over 99% of the propofol is inthe particles. Other cases would include where the active compound issensitive to hydrolysis, oxidation, electrolysis, cavitation, or broadlyany form of chemical attack from species (ions, nucleophiles,electrophiles, radicals, etc.) which are more polar and localizepreferentially in the aqueous phase. The general approach is to dilutethe drug in the particles with a compound, preferably a liquid or atleast a low-melting compound, that has a high partition coefficient,preferably greater than about 10, more preferably greater than about100, and most preferably greater than about 1,000. This increases thevolume of hydrophobic material in the particles and in the dispersionrelative to the mass of drug, irregardless of whether the diluentcompound has a particular affinity or solubilization potential for thedrug (provided that the drug is soluble in, or miscible with, thediluent). What makes this approach work effectively and efficiently inthe context of this invention is the fact that the high-K_(ow) diluentcan be chosen such that it mimics the molecular polar-to-apolar groupratio of the drug, so that the reversed cubic or reversed hexagonalphase can be found with the diluent-drug combination at the same, orsimilar, volume fraction as that in the system without diluent. Forinstance, in Example 19 below, a reversed cubic phase in the PluronicL-122/propofol/water system is found with the drug propofol atapproximately 19% by volume, or alternatively, in the system withdiluent, at a total propofol (10%) plus tocopherol (9%) volume fractionalso of approximately 19%. Similarly, in Example 20, a reversed cubicphase in the phosphatidylcholine/propofol/water system is found with thedrug propofol at approximately 29% by volume, or alternatively, in thesystem with diluent, at a total propofol (10%) plus tocopherol (19%)volume fraction also of approximately 29%. This is particularlyimportant in cases where the extent of the desired liquid crystallinephase region in composition space (i.e., the phase diagram) isrelatively small. In making this dilution, it is highly preferable whenthe diluent is chosen so as to mimic the drug molecule in terms of theratio of polar groups to apolar groups. For example, tocopherol, withits benzopyranol group (2 oxygens) as part of a 430-MW compound issimilar in polar/apolar ratio to propofol, with its single phenolicgroup (1 oxygen) as part of a 178-MW molecule. Polar groups such ashydroxyls are believed to bind strongly to the polar-apolar interface ofsurfactant-water systems, and since this has important implications forphase behavior [see, for example, P. Strom and D. M. Anderson, Langmuir(1992) 8:691-702], the diluent should preferably have a similar contentof similar polar groups, to the extent possible.

In cases where the active is propofol, and with other drugs andnutrients which are given to patients for whom the intake of lipids mustbe controlled, it is an important advantage of many of the formulationsreported herein that the lipid loads can be made very low, Particularlyin the Pluronic-based cubic phase formulations, reported in Examples1-4, and 13-17, the lipid load is significantly lower than in thecurrently marketed formulations, and furthermore this can reduced byincorporating up to 19% propofol in the cubic phase without anyalpha-tocopherol. Particularly in applications of propofol where it isused repeatedly or continuously over time as a sedative, lipid loadsfrom the formulation can significantly interfere with the patient'snutritional regiment or even cause serious complications.

Alpha-tocopherol, or other forms of vitamin E such as tocopherol acetateand tocopherol succinate, is a highly preferable choice as ahigh-partition-coefficient diluent for injectable products because ofits long history of safe use in injectable products, as well as theinterface-bound OH group cited above. Other preferred diluents includeessential oils of plant origin, as well as a number of other liquidsthat are listed on FDA's list entitled Inactive Ingredients forCurrently Marketed Drug Products and/or the appropriate sections of theFood Additives Status List. Among these are: benzyl benzoate, cassiaoil, castor oil, cyclomethicone, polypropylene glycol (of low MW),polysiloxane (of low MW), cognac oil (ethyl oenanthate), lemon balm,balsam of Peru, cardamom oleoresin, estragole, geraniol, geraniolacetate, menthyl acetate, eugenol, isoeugenol, petigrain oil, pine oil,rue oil, trifuran, annato extract, turmeric oleoresin, and paprikaoleoresin. Essential oils from plant sources (including their extractsand components, and mixtures thereof) comprise a rather large andchemically diverse group of liquids that include many low-toxicityhydrophobes with polar groups. The term “essential oils” is intended toinclude essential oils from the following sources: allspice berry, amberessence, anise seed, arnica, balsam of Peru, basil, bay, bay leaf,bergamot, bois de rose (rosewood), cajeput, calendula (marigold pot),white camphor, caraway seed, cardamon, carrot seed, cedarwood, celery,german or hungarian chamomile, roman or english chamomile, cinnamon,citronella, clary sage, clovebud, coriander, cumin, cypress, eucalyptus,fennel, siberian fir needle, frankincense (olibanum oil), garlic, rosegeranium, ginger, grapefruit, hyssop, jasmine, jojoba, juniper berry,lavender, lemon, lemongrass, lime, marjoram, mugwort, mullein flower,myrrh gum, bigarade neroli, nutmeg, bitter orange, sweet orange, oreganopalmarosa, patchouly, pennyroyal, black pepper, peppermint, petitegrain,pine needle, poke root, rose absolute, rosehip seed, rosemary, sage,dalmation sage, santalwood oil, sassafras (saffrole-free), spearmint,spikenard, spruce (hemlock), tangerine, tea tree, thuja (cedar leaf),thyme, vanilla extract, vetivert, wintergreen, witch hazel (harnamelia)extract, or ylang ylang (cananga). The following components of essentialoils are also preferred: 2,6-dimethyl-2,4,6-octatriene;4-propenylanisole; benzyl-3-phenylpropenoic acid;1,7,7-trimethylbicyclo[2.2.1]heptan-2-ol;2,2-dimethyl-3-methylenebicyclo[2.2.1]heptane;1,7,7-trimethylbicyclo[2.2.1]heptane;trans-S-methyl-n-vanillyl-6-nonenamide;2,2,5-trimethylbicyclo[4.1.0]hept-5-ene; 5-isopropyl-2-methylphenol;p-mentha-6,8-dien-2-ol; p-mentha-6,8-dien-2-one; beta-caryophyllene;3-phenylpropenaldehyde; 3,7-dimethyl-6-octenal;3,7-dimethyl-6-octen-1-ol; 4-allylanisole; ethyl 3-phenylpropenoic acid;3-ethoxy-4-hydroxybenzaldehyde; 1,8-cineole; 4-allyl-2-methoxyphenol;3,7,11-trimethyl-2,6,10-dodecatrien-1-ol;1,3,3-trimethylbicyclo[2.2.1]heptan-2-ol;1,3,3-trimethylbicyclo[2.2.1]heptan-2-one;trans-3,7-dimethyl-2,6-octadien-1-ol;trans-3,7-dimethyl-2,6-octadien-1-yl acetate;3-methyl-2-(2-pentenyl)-2-cyclopenten-1-one; p-mentha-1,8-diene;3,7-dimethyl-1,6-octadien-3-ol; 3,7-dimethyl-1,6-octadien-3-yl acetate;p-menthan-3-ol; p-menthan-3-one; methyl 2-aminobenzoate;methyl-3-oxo-2-(2-pentenyl)-cyclopentane acetate; methyl2-hydroxybenzoate; 7-methyl-3-methylene-1,6-octadiene;cis-3,7-dimethyl-2,6-octadien-1-ol;2,6,6-trimethylbicyclo[3.1.1]hept-2-ene;6,6-dimethyl-2-methylenebicyclo[3.1.1]heptane; p-menth-4(8)-en-3-one;p-menth-1-en-4-ol; p-mentha-1,3-diene; p-menth-1-en-8-ol; ethylmethylphenylglycidate; and 2-isopropyl-5-methylphenol.

Especially preferred diluents, due to a favorable combination of gooddrug-solubilizing properties, low toxicity, low water solubility, usefultemperature range as a liquid, history of use, and compatibilty with (orinduction of) cubic and hexagonal phases, are: tocopherols, benzylbenzoate, estragole, eugenol, isoeugenol, linalool, strawberry aldehyde,terpineol, and the following essential oils: balsam of Peru, basil, bay,hois de rose (rosewood), carrot seed, clovebud, eucalyptus, ginger,grapefruit, hyssop, lemon, mugwort, myrrh gum, bitter orange, oregano,palmarosa, patchouly, peppermint, petitgrain, rosemary, santalwood oil,spearmint, thuja (cedar leaf), thyme, vanilla, and ylang ylang(cananga). Of these, the present inventor has found tocopherols,linalool, and strawberry aldehyde (ethyl methylphenylglycidate) to bethe most preferred in the case of injectable products.

Example 18 shows an experimental result which indicates that theexterior-phase concentration of the general anesthetic drug propofol inseveral cubic phases equilibrated with water is strongly reduced byreplacing approximately half of the propofol with alpha-tocopherol. InExamples 19 and 20, propofol formulations of the instant invention inwhich the same tocopherol-propofol mixture was used in the cubic phaseparticles were injected intravenously in dogs, and no discomfort oninjection was noted in any of the animals. As noted above, the consensusin the art is that the stinging on injection of many propofolformulations is due to the propofol present in the aqueous phase. Thisunderscores the importance of control of oil-water partitioning that ispossible in the current invention, by a simple means. The same method isalso applicable to other systems containing surfactants or lipids, suchas liposomes, coated liquid crystal particle dispersions,microemulsions, and emulsions. It is not necessary that the diluent haveany particular affinity for the drug, as illustrated by the examplesherein where tocopherol is the diluent, since this compound has nospecial affinity for propofol (nevertheless, as discussed above,propofol and tocopherol share one structural similarity that isimportant in the context of this invention). Rather the effect is themathematical result of the increased ratio of hydrophobic volume to drugmass. As seen by the data in Example 18, increasing the ratio ofhydrophobic volume (volume fraction of hydrophobic domains) to drugcontent (volume fraction of drug) by 50%, or more preferably by 100%,can have a strong effect on the concentration of drug in the exteriorphase. Tocopherols are particularly useful as diluents in a wide rangeof possible systems because of their long hydrophobic chains, lowmelting points, and safe, non-allergenic nature. While the use of oilydiluents is known in the art of emulsions, their use in the context ofliposomes and liquid crystal-based dispersions has been virtuallyunknown, particularly in the field of pharmaceutics, with the exceptionof certain patent disclosures of the current inventor (U.S. applicationSer. No. 10/176,112 and 60/387,909).

Another surprising finding in the course of preparing the samplesreported herein was that the oxidation of propofol over time wasstrongly reduced by the use of the tocopherol diluent method describedabove. This could be due to a combination, perhaps a synergistic one, ofseveral factors. The tocopherol itself can act as an antioxidant, and inparticular can protect the propofol when it is in the hydrophobicdomains of the dispersion. In addition, the reduction of aqueouspropofol by the diluent method can reduce the rate of oxidation due tothe slower oxidation kinetics in the hydrophobic domains as compared tothe aqueous phase. due to higher viscosity and/or lower concentration ofoxygen. The second factor would apply even in cases where the diluentwere not specifically an antioxidant.

Tonicity Adjustment. In the course of this invention, the inventor hasfound that soluble amino acids, e.g. glycine, praline, and valine, inparticular, are excellent tonicity adjusters for formulations thatincorporate surfactants containing polyethyleneoxide (or PEG) polargroups, such as Poloxamers (Pluronics), particularly in the case ofpropofol formulation. The reasons that soluble, and especially neutralhydrophilic, amino acids are particularly useful in these cases are: 1)they do not suffer from the tendency to precipitate particlesincorporating PEGylated surfactant, as do ionic salts; 2) they do notappreciably increase, and in fact they can decrease, the concentrationof propofol in the exterior aqueous phase, which as discussed herein isimportant in reducing burning on injection; and 3) they appear to havethe effect of improving the compatibility of the reversed cubic andhexagonal phases with the aqueous phase. Example 18 demonstrates thereduction of aqueous propofol with the addition of glycine to make thedispersion isotonic (about 300 mOsm/L). In contrast, it was found thatsaccharides which are commonly used to adjust tonicity, such asdextrose, increased aqueous levels of propofol. Even 0.8% sodiumchloride had the effect of precipitating Pluronic L-122/deoxycholateparticles of the present invention over a period of about one week.Glycine was also discovered to yield a more transparent cubic phase,indicating more perfect long-range order, in these experiments. Glycineand valine and proline were found to have no adverse effects onpropofol-containing, L-122 based cubic phase particles of the currentinvention. Glutamine and asparagine were disruptive of the sameformulation. Glycine is used in large amounts (greater than 100 mg/Kg)in injections of the pharmaceutical product Humate-P, and a single doseof the injectable nutritional product Nephramine contains more than 2grams of the valine, making both especially preferred for parenteralproducts. Preferred amino acids for this purpose, in decreasing order ofpreference, are: glycine, alanine, proline, serine, glutamine, valine,asparagine; the acidic, basic, and hydrophobic amino acids are much lesspreferred (and some of these are not soluble in water totonicity-adjusting levels), as are sulfur-containing amino acids becauseof hypersensitivity issues. The amino acids listed as preferred alsohave a pH-stabilizing effect, and can act as antioxidants to someextent. The use of glycine at levels between about 1 and 3%, and morepreferably between about 1.3 and 2.2%, is preferred for adjustingtonicity, unless other components are present that add to the osmolalityin which case lower levels can be useful. The synergy between thevarious functionalities of these amino acids—namely their compatibilitywith PEG head groups, their positive effect on drug partitioning (atleast in the case of phenolic drugs such as propofol), and theirtonicity, buffering, and antioxidant activity is particularly importantin the case of pharmaceutical products, where the impetus is high tokeep the number of components in the formulation to a minimum. Tonicitymight also be achieved with the use of zwitterions, includingphoshpatidylcholine.

An especially useful method of producing particles of the presentinvention involves related phases of lower viscosity. In particular, andas illustrated in Example 17 below, it is often the case that when wateris removed from a reversed cubic or hexagonal phase, a muchlower-viscosity, liquid L2 phase is formed, or in rarer cases a liquidL3 phase. This is, in some cases, merely a reflection of the fact thatsurfactant head groups require hydration in order for the segregationinto hydrophobic and hydrophilic domains to be pronounced enough,energetically speaking, for full-blown liquid crystalline phase behaviorto develop. Since the liquid L2 phase is of low viscosity it is muchmore easily dispersed in water, and after the resulting droplets hydratewith water, they undergo the phase change into the sought-after reversedliquid crystalline phase. This hydration is generally a rapid processbecause the diffusion times are greatly reduced, assuming a reasonablyfine L2-phase droplet size is achieved, preferably less than about 100microns and more preferably less than about 20 microns. The same chargedmoiety that induces the charge stabilization in the final liquidcrystalline particle dispersion can likewise provide chargestabilization of the liquid droplets in dispersion. Other methods can beused to convert the precursor liquid (usually L2, or in other cases L3phase) droplets into liquid crystalline phase particles. These include,for example, incorporating a low-partition-coefficient compound into theliquid crystal causing it to liquify, where the low K_(ow) implies thatthe compound will preferentially leave the liquid droplets upondispersing, inducing the liquid to revert to a liquid crystal as aparticle. Such a compound can easily be found simply by addingsufficient quantity of a low-K_(ow) compound to a liquid crystal untilthe liquid crystal liquifies, which is not a difficult endeavor in viewof the typically small composition range of reversed liquid crystallinephases.

Stability studies reported in Example 22 demonstrate that particles ofthe instant invention are stable long-term in dispersion, with verylittle aggregation or particle size growth over time, as shown bydynamic light scattering measurement, which is well known to be verysensitive to particle aggregation. It should be noted that this standsin contrast with the cubic gel particles of U.S. Pat. No. 6,071,524which are in fact designed to aggregate at the surface of the oildroplets in that invention. Stability studies with particle sizingresults over time were not provided in U.S. Pat. No. 6,071,524.

The following examples illustrate the present invention but are not tobe construed as limiting the invention.

Examples Example 1

A reversed cubic phase containing the anesthetic propofol was firstprepared by mixing 0.952 grams (gins) of propofol (obtained fromAlbemarle Corporation), 1.308 gm of distilled water (all references towater in this section mean distilled water), and 2.756 gm of thesurfactant Pluronic L122 (obtained from Ethox Corporation). Afterthoroughly mixing this composition, it was checked that the material wasoptically isotropic and of high viscosity. Next, 0.319 gm of the anionicsurfactant sodium docusate (also known as Aerosol OT, or simply AOT) wasdissolved in 100 ml of water, Then 1.088 gm of the cubic phase was addedto a 100 ml beaker containing 20 ml of the surfactant solution, and themixture homogenized using a Brinkmann PT 10/35 homogenizer, after whichthe homogenized dispersion was microfluidized in a Microfluidics Model110L high-pressure microfluidizer, using three runs of 30 seconds eachat approximately 10,000 psi. Observation in an Olympus BHC phasecontrast microscope demonstrated that a particle size on the order of300 nanometers (nm) had been achieved. The dispersion was then analyzedusing a Beckman-Coulter DELSA 440SX for Doppler Electrophoretic LightScattering Analysis, set in zeta potential measurement mode.

FIG. 3 shows the resulting measured zeta potential distribution, usingthree angles of measurement. At all three angles, the distribution iscentered around −67 mV, which is a strong enough zeta potential toproduce a stable dispersion. It should be noted that although there is aspread to the distribution, significant contributions to this reportedspread come from instrumental broadening, and diffusional broadening.Therefore the distribution is in fact significantly narrower thanindicated. Particularly with this in mind, the fraction of particleswith a zeta potential less than 30 mV in magnitude is quite small.

The ratio of surfactant (docusate) to cubic phase in this Example was0.06:1, and a stable dispersion resulted, with an average zeta potentialof −67 mV. When this ratio was decreased to 0.02:1, keeping everythingelse constant, the average zeta potential moved to approximately −20 mV,and that dispersion was not stable.

Example 2

The general anesthetic and hypnotic agent propofol, in the amount 0.57grams, was combined with 0.78 gm sterile water and 1.65 gm of PluronicL122 (in which the weight fraction of polyoxyethylene chains is 20%),working in a laminar flow hood. After mixing this to form a reversedcubic phase, 0.105 gm of sodium deoxycholate were dissolved in 40 nil ofsterile water. An amount 2.1 gm of the cubic phase were then dispersedin the 40 ml of solution, first using the Brinkmann homogenizer, thenusing the Microfluidics microfluidizer for a total of 15 minutes ofhigh-pressure microfluidization. The dispersion, referred to below as“Lyotropic/PF1”, was filtered with a 0.8 micron syringe filter beforeusing in the animal tests described in Example 4 below.

FIG. 4 shows the zeta potential distribution measured for thisdispersion. The average zeta potential, namely about −48 mV, is greaterin magnitude than 30 mV and thus consistent with stabilization dueprimarily to the surface potential.

A mixture was also prepared with only 1 ml of water but the same amountof sodium deoxycholate. Thus, all the ratios were the same as in theprevious paragraph, except the amount of water. The purpose of this isto check the phase behavior in the presence of excess water (this isenough to give an excess), but without the dispersing/diluting effectthat comes with the normal 20:1 water:cubic phase ratio. This means thatif any L3 or lamellar phase were present, while it might be difficult todetect in the dilute dispersion, it would be far easier to detect inthis concentrated form. This was analyzed in an Olympus BHC polarizingoptical microscope, and the result shown in FIG. 5. On the left is athick line of birefringence, which is a single strand of hair,deliberately placed in the field of view to show what a birefringentmaterial would appear like under these optical/photographic conditions.The contrast clearly shows that material of this invention isnon-birefringent. Neither was there birefringence when the sample wassheared between glass and coverslip, showing that there is no L3present. In addition, when the sample was centrifuged, there did notappear to be any signs of a separate L3 in the centrifuged sample,rather it appeared to be simply a mixture of cubic phase plus excessaqueous solution.

Example 3

Propofol, in the amount 0.57 grams, was combined with 0.78 gm sterilewater and 1.65 gm of Pluronic P123 (in which the weight fraction ofpolyoxyethylene chains is 30%), working in a laminar flow hood. Aftermixing this to form a reversed cubic phase, 0.105 gm of sodiumdeoxycholate were dissolved in 40 ml of sterile water. An amount 2.1 gmof the cubic phase were then dispersed in the 40 ml of solution, firstusing the Brinkmann homogenizer, then using the Microfluidicsmicrofluidizer for a total of 15 minutes of high-pressuremicrofluidization. The dispersion, referred to below as “Lyotropic/PF4”was filtered with a 0.8 micron syringe filter before using in the animaltests described in Example 4 below. DELSA analysis shown a unimodal zetapotential distribution centered at approximately −36 mV.

Example 4

In this Example, rats were dosed with the formulations reported above inExamples 2 and 3, and these formulations were found to outperform acurrently marketed, emulsion-based formulation of propofol, yielding afaster return to normal awareness after anesthesia, in contrast to theslower return noted for the marketed brand. A total of 18 Sprague Dawleyrats were administered Lyotropic/PF1, LyotropicfPF4 or Propoflo® (thecommercially available propofol formulation) via the lateral tail veinonce at dose levels ranging from 0.5 to 12 mg/kg in an up-down fashion.The rats were housed in stainless steel cages with wire mesh floorssuspended over flush pans and identified by a unique number marked ontheir tail with indelible ink in addition to a cage card inscribed withthe animal number, study number, group number and color-coded doselevel. The animals were maintained in an isolated temperature (16-23 C)and humidity (53%-71%) controlled animal room with a filtered air supply(10-15 air changes/hour) and cycled lighting (12 hours daily). PMICertified Rodent Diet (5002) and tested tap water were available adlibitum. Food was withheld overnight prior to dosing. Rats used in thisstudy were acclimated to laboratory conditions for at least 5 days priorto animal phase initiation. The rats were selected on the basis ofpretest body weight and general appearance and randomly assigned to thefollowing groups:

Dose No. of Group Doses Conc. Rats/Dose Number Test Article mg/kg mg/mLLevel CBF1 Lyotropic/PF1 0.5, 1, 2, 4, 8 1 or 10* 2 CBF3 Propoflo ® 4, 810 2 CBF4 Lyotropic/PF4 2, 4, 8 10 2 *For rats dosed at 0.5, 1 and 2mg/mL, the test article was diluted with Sterile Water for Injection fora final dose concentration of 1 mg/mL. The final dose concentration forrats dosed at 4 and 8 mg/mL was 10 mg/mL.

Body weights were obtained just prior to dose administration and wereused as the basis for dosing. The animals were observed immediatelypostdose and continuously up through 30 minutes, and again atapproximately I, 2 and 24 hours postdose for general health, physicalappearance and for signs of clinical effect, including behavioralchanges. Parameters for evaluation included postdosing observations andgross observations at necropsy.

No mortality occurred during the 24-hour postdosing observation period.Relevant signs of effect included ataxia, comatose, decreased activity,and squinting of the eyelid(s), which were all resolved by 24 hourspostdosing. In most cases, the time of the comatose condition was rapidfollowing intravenous injection and generally increased in adose-dependent manner. Gross necropsy observations revealed noremarkable findings. In particular, no signs of pulmonary emboli werefound in any of the test animals, including those treated with the cubicphase dispersion formulations.

Significantly, the animals dosed with Lyotropic/PF1 appeared, to anobserver trained in anesthesiology, to emerge from the coma with greaterclarity and “clear-headedness” than the animals dosed with Propotlo®.Without wishing to be bound by theory, it is believed that this was dueto the integration of the uncoated reversed cubic phase vehicle withbiomembrane structures in the body, resulting in the elimination of thevehicle as a “depot”, or reservoir, for drug. In contrast, the marketedemulsion formulation is believed to suffer from effects due to alingering reservoir effect from the oil droplets.

The Body Weight and Dosing Records (Table 1), Individual PostdoseClinical Signs (Table 2) and Time of Comatose Condition (Table 3) aregiven below.

TABLE 1 Body Weight and Dosing Records Dose Animal No. Body Weight DoseConcentration Dose Volume Prefix: CBF (g) (mg/kg) (mg/mL) (mL/kg)Lyotropic/PF1 1M1 259.2 0.5 1 0.5 1F17 222.5 0.5 1 0.5 1M5 265.5 1 1 11F21 221.1 1 1 1 1M9 265.4 2 1 2 1F25 231.9 2 1 2 1M13 273.1 4 10 0.41F29 235.8 4 10 0.4 1M33 299.1 8 10 0.8 1F34 203.2 8 10 0.8 Propoflo ®3M3 237.7 4 10 0.4 3F19 220.1 4 10 0.4 3M7 253.8 8 10 0.8 3F23 222.5 810 0.8 Lyotropic/PF4 4M12 275.3 2 10 0.2 4F28 229.2 2 10 0.2 4M16 271.84 10 0.4 4F32 242.0 4 10 0.4 4M35 283.3 8 10 0.8 4F36 215.3 8 10 0.8

TABLE 2 Individual Postdose Clinical Signs 0-30 Min Animal No. DosePost- 1 Hour 2 Hours 24 Hours Prefix: CBF Test Article (mg/kg) dosingPostdosing Postdosing Postdosing* 1M1 Lyotropic/PF1 0.5 DA, ES NR NR NR1F17 Lyotropic/PF1 0.5 DA, ES NR NR NR 1M5 Lyotropic/PF1 1 DA NR NR NR1F21 Lyotropic/PF1 1 DA NR NR NR 1M9 Lyotropic/PF1 2 DA NR NR NR 1F25Lyotropic/PF1 2 DA NR NR NR 1M13 Lyotropic/PF1 4 CT, DA NR NR NR 1F29Lyotropic/PF1 4 CT, DA NR NR NR 1M33 Lyotropic/PF1 8 AT, CT NR NR NR1F34 Lyotropic/PF1 8 AT, CT NR NR NR 3M3 Propoflo ® 4 AT NR NR NR 3F19Propoflo ® 4 AT, CT NR NR NR 3M7 Propoflo ® 8 AT, CT NR NR NR 3F23Propoflo ® 8 AT, CT NR NR NR 4M12 Lyotropic/PF4 2 DA NR NR NR 4F28Lyotropic/PF4 2 DA NR NR NR 4M16 Lyotropic/PF4 4 AT, DA DA NR NR 4F32Lyotropic/PF4 4 AT, CT NR NR NR 4M35 Lyotropic/PF4 8 AT, CT, NR NR NR DA4F36 Lyotropic/PF4 8 AT, CT NR NR NR Key to observations: AT = Ataxia CT= Comatose DA = Decreased activity ES = Eyelid(s) squinting NA = Notapplicable NR = Not remarkable *Just prior to necropsy

TABLE 3 Length of Comatose Condition Animal No. Dose Time of ComotosePrefix: CBF Test Article (mg/kg) (min) 1M13 Lyotropic/PF1 4 3 1F29Lyotropic/PF1 4 4 1M33 Lyotropic/PF1 8 4.5 1F34 Lyotropic/PF1 8 5.5 3F19Propoflo ® 4 1 3M7 Propoflo ® 8 5 3F23 Propoflo ® 8 5.5 4M35Lyotropic/PF4 8 4 4F36 Lyotropic/PF4 8 8 4F32 Lyotropic/PF4 4 2

Example 5

A reversed cubic liquid crystalline phase was prepared by thoroughlymixing 0.962 gin of propofol, 0.706 gm water, and 1.329 gm of soyphosphatidylcholine (from Avanti polar lipids). An amount 1.002 gm ofthis cubic phase was placed in a 100 ml beaker containing 20 ml ofaqueous sodium docusate (Aerosol OT), wherein the ratio of docusate tocubic phase was 0.06:1. The mixture was homogenized at high speed for 45seconds, then microfluidized for 6 minutes, producing a fine dispersion,with a substantial submicron population. This was analyzed with theDELSA instrument and found to have an average zeta potential of about−67 mV, as shown in FIG. 6. It should be noted that under the conditions(in particular, pH) used, the phosphatidylcholine/propofol/water cubicphase would, as in the previous Examples, be substantially uncharged, sothat the docusate is required for the attainment of a charge-stabilizedcubic phase particle dispersion. Indeed, it is impossible to dispersethis cubic phase without the use of a charged, bilayer-associatedcompound even at the highest shear rates possible with thisinstrumentation. Quickly after any attempt, no matter how vigorous, todisperse this cubic phase, the cubic phase material agglomerates backinto macroscopic clumps. All of the components (except the drug) in thisformulation are on the FDA list of approved excipients for injectableproducts.

Example 6

Another 1.002 gm of the cubic phase from Example 5 was dispersed in 20ml of a solution of benzalkonium chloride using the same methodology asin Example 5. The average zeta potential was then measured and found tobe about +74 mV, as shown in FIG. 7.

Example 7

The local anesthetic bupivacaine, in its free base form, and in theamount 0.176 gm, was combined with 0.700 gm linalool, 0.333 gmsantalwood oil, 1.150 gm water, and 2.65 gm of the surfactant PluronicL122. The resulting cubic phase is thus composed of excipients of verylow toxicity; even santalwood oil has been shown to be of low toxicityby injectable routes (though it is not strictly speaking approved foruse in injectable products). Using the methodology of the previousExamples, this cubic phase was dispersed using sodium docusate (at a0.06:1 ratio), and the zeta potential measurement taken. FIG. 8 showsthe result, which indicates a distribution centered around −64 mV, andnearly all particles more negative than −30 mV.

Example 8

The cubic phase from Example 7 was dispersed, using similar physicalmethods, using the cationic surfactant benzalkonium chloride. Theresulting zeta potential distribution, shown in FIG. 9, was centeredaround +55 mV, for the dispersion of charged-stabilized particles.

Example 9

A cubic phase containing the active vitamin E was prepared by mixing1.12 gm of vitamin E (alpha-tocopherol), 1.593 gm of soyphosphatidylcholine, and 0.788 gm of water. This was dispersed usingbenzalkonium chloride, and a zeta potential average of roughly +70 mVwas recorded.

Example 10

The same cubic phase as in Example 9 was stirred vigorous together withone-tenth its weight in sodium dantrolene, a skeletal muscle relaxant.This was then dispersed in aqueous benzalkonium chloride, with a 20:1ratio of water to cubic phase, and a 0.06:1 ratio of surfactant to cubicphase. This was homogenized at high speed for 3 minutes.

Zeta potential is particularly meaningful in this case, since the drugis anionic, whereas the dispersed cubic phase (as in Example 9) iscationic. Therefore, if “free” dantrolene is present then a peak willappear with a negative zeta potential, together with the peak from thecationic-stabilized particles, indicating that particles of thisinvention have not been produced.

In fact, the strongly-colored (from the dantrolene sodium) dispersionwas analyzed with the DELSA, and no peak was found at negative zetapotential. FIG. 10 shows the analysis, with a single peak (at all fourangles) centered at +72 mV. Thus, particles of the present inventionwere indeed produced, with nanosized crystals of the poorly-solubleskeletal muscle relaxant stabilized by their being embedded in acationically-stabilized cubic phase particle of the current invention.

An attempt to disperse dantrolene sodium with only the benzalkoniumchloride, not using the cubic phase or any other liquid crystal, wasmade in order to evaluate the importance of the cubic phase in thisExample. Thus, dantrolene sodium was dissolved in the aqueous phase atthe same concentration, resulting in a 0.06:1 ratio of surfactant todantrolene sodium, and the same homogenization protocol was applied. TheDELSA measurement, shown in FIG. 11, clearly shows a much smaller zetapotential than in the case where the cubic phase was used. This greatlyincreased charge in the case of the cubic phase particle is probablyrelated to the much higher benzalkonium loading possible with the cubicphase (as expressed at the particle surface) as compared to thedantrolene sodium surface.

Dantrolene sodium is presently used in the treatment of malignanthyperthermia, a life-threatening, crisis situation. The currentlymarketed formulation must be reconstituted one vial at a time, with asmany as 36 vials being required for a single treatment. Patient deathshave been reported caused by the physician being unable to reconstitute,and inject this many vials during the mounting MH crisis. The presentinvention may provide a means by which a stable, concentrated dispersionof the drug could be injected in place oldie current formulation. Whileother methods of stabilizing nanocrystals of compounds such asdantrolene are available, the current invention can have advantages overthese in cases where the absorption-enhancing properties of the currentinvention are desirable. All of the components of this formulation arepharmaceutically-acceptable for intravenous injection.

Example 11

An amount 0.999 grams of the L122/propofol/water cubic phase used inExample 1 was dispersed in a solution of sodium dodecylsulfate (SDS), atan SDS:cubic phase ratio of 0.06:1. This produced a stable dispersion ofmicroparticles with a zeta potential centered at approximately −63 mV,as shown in FIG. 12. SDS is not only a very low toxicity surfactant,which is approved for use in injectable products, but is also one of themost, if not the most, well-studied and characterized surfactantsavailable.

Example 12

The antineoplastic drug paclitaxel, in the amount 40 mg, was combinedwith 0.372 gm of santalwood oil and 0.725 gm of strawberry aldehyde,then heated to dissolve the paclitaxel. This was then combined with1.855 gm of Plutonic L122 (HLB=4) and 0.905 gm of water, and mixed toform a reversed cubic phase. This was then then dispersed in an aqueoussolution of sodium docusate at a docusate:cubic phase ratio of 0.06:1,by homogenizing at high speed for 30 seconds, then microfluidizing for1.5 minutes, and finally centrifuging for 5 minutes in a table-topcentrifuge at about 5,000 rpm. DELSA analysis (using a current of 0.18mA, and a frequency shift of 500 Hz) then indicated a zeta potentialdistribution centered around −53 mV, as shown in FIG. 13. Thiscremophor-free formulation of paclitaxel could be well-suited for anumber of routes of administration, including bladder instillation,intraperitoneal, peroral, or possibly by injection.

Example 13

A reversed cubic phase containing the anesthetic propofol was firstprepared by mixing 0.9501 grams of propofol (obtained from the AlbemarleCorporation), 1.2970 gm of distilled water, and 2.7575 gin of thesurfactant Pluronic P-123 (a poloxamer surfactant obtained from the BASFCorporation). After thorough mixing, the composition was checked toensure that it had high viscosity and was optically isotropic. It wasthen loaded into a 10 mL disposable syringe to facilitate weighing of a1 gin sample. In another beaker, 0.3192 gm of Aerosol OT (AOT, alsocalled docusate sodium) were dissolved in 100 mL of distilled water. Astir bar was placed in the beaker and the solution was stirred for 1hour using a Fischer Thermix Model 210T. An amount of 1.0199 gm of thecubic phase was then added to the solution of AOT and water in an amountequivalent to 0.0638 gm AOT and 20.0 gm of distilled water. Thisresulted in a 0.06:1 surfactant to cubic phase ratio and a 20:1distilled water to cubic phase ratio. The mixture was homogenized usinga Brinkman PT 10/35 homogenizer on high for 20 seconds. The homogenizeddispersion was then microfluidized with a Microfluidics M110L for 3runs, each of which lasted for 30 seconds. Next, the dispersion wascollected in a test tube and centrifuged for 2 minutes using a tabletopcentrifuge. The dispersion was viewed under an Olympus BHC microscope tocheck for particle appearance and size.

The dispersion was then analyzed by using the Beckmann-Coulter DELSA440SX for Doppler Electrophoretic Light Scattering Analysis, withelectrophoretic mobilities converted to zeta potentials by the standardequations, as seen in FIG. 14. Four scattering angles of measurementwere reported, with the distribution in each case centered aroundnegative 39 mV. This electrophoretic mobility analysis was run at afrequency shift, as per the Beckmann-Coulter DELSA methodology, of 500Hz, with a runtime of 180 seconds. Docusate appears on the 1996 FDA'sInactive Ingredients Guide as approvable for use in injectable products.

Example 14

Using methods similar to those employed in preparing Example 13, anamount of 1.0135 grams of the cubic phase identical to that from Example13 were added to an equivalent of 0.0638 gm Sodium Dodecyl Sulfate(SDS)(obtained from the EM Science Corporation) and 20.0 gm of distilledwater as described in Example 13.

Again, using similar methods to Example 13, the dispersion washomogenized, microfluidized, and analyzed under the microscope. The zetapotential was found to be negative 41 mV, as measured from four anglesat 500 Hz for 180 seconds. It should be noted that SDS has been used inthe injectable pharmaceutical product Proleukin.

Example 15

Again, using methods similar to those employed in Example 13, an amountof 1.0001 grams of the cubic phase identical to that from Example 13were added to an equivalent 0.0638 gm of Benzalkonium Chloride (obtainedfrom the Sigma Corporation) and 20.0 gm of distilled water as describedin Example 13. Benzalkonium chloride has been used in the injectableproduct Celestrone Soluspan.

Following the methods described in Example 13, the dispersion washomogenized, microfluidized, and analyzed under the microscope. The zetapotential for this dispersion was found to be 36 mV and thus indicatedcharge stability. It was run at 500 Hz for 180 seconds from fourdifferent scattering angles.

Example 16

The same methods as were used for the preceding Example were used hereto prepare a similar cubic phase except 0.9520 grams of Pluronic L-122were used in place of the 0.9501 gm of Pluronic 123. An amount of 0.9989gm of the cubic phase were then added to 0.0638 gm of benzalkoniumchloride (obtained from the Sigma Corporation) and 20.0 gm of distilledwater.

Methods similar to those utilized in Example 13 were used tomicrofluidize, homogenize, and analyze the dispersion under themicroscope. The zeta potential of the dispersion, taken at fourdifferent angles and run at 500 Hz for 180 seconds, averaged +47 mVwhich indicated charge stability as per the instant invention.

Example 17

This Example illustrates the method of production discussed above, inwhich a low-viscosity liquid phase precursor to the reversed liquidcrystalline phase is prepared and dispersed, and the particles convertto the liquid crystalline phase after contact with water. An L2 phasewas first prepared by mixing 2.2009 grams of propofol, 1.9883 grams ofalpha-tocopherol, and 12.0964 grams of the poloxamer surfactant EthoxL-122 into a 50 mL test tube and vortexing until it was all one phase.The liquid L2 phase that formed was clear but yellow and of lowviscosity. In a 150 mL beaker were placed 0.9032 grams of sodiumdeoxycholic acid, 2.0017 grams of glycine, 70 mL of distilled water, and13.345 grams of the L2 phase. This was homogenized until the materialwas dispersed. Under observation in Differential Interference Contrast(DIC) in a Reichert-Jung Polyvar microscope, it was evident that the L2phase had turned to a viscous and rigid cubic phase, withirregularly-shaped, angular particles in contrast with liquid dropletswhich are quite generally round. This was then further homogenized for60 more minutes, and the particle size then was small enough that thematerial could be filtered through a 0.22 micron filter easily. The zetapotential distribution measured as described above was unimodal andcentered at approximately −34 mV.

Example 18

Four reversed cubic phases were prepared with propofol (AlbemarleCorporation), alpha-tocopherol (Vitamin E, from Aldrich ChemicalCompany), distilled water and Pluronic L122 (Ethox Corporation). Thepropofol and vitamin E were combined in various ratios by weight tototal 19%, the water was held constant at 26% and the Pluronic L-122 at55%. The ingredients were combined in 8mL test tubes and thoroughlymixed until optically isotropic and of high viscosity. A total of threegrams of each of the following compositions were prepared (all weightslisted in grams):

10% 19% propofol 13% propofol 16% propofol propofol propofol 0.302 0.3880.478 0.570 vitamin E 0.273 0.189 0.105 0 distilled water 0.777 0.7920.786 0.784 pluronic L122 1.657 1.649 1.658 1.647

A thin layer of each reversed cubic phase was smeared onto the insidewall of four test tubes, and an appropriate amount of solvent (eitherdistilled water or 2.2% glycine solution—the later prepared by adding48.9 mL of distilled water to 1.1 g of glycine, Spectrum ChemicalCompany) was added to each tube to obtain an overall 1% or 2% propofolconcentration. Thus, the following sixteen combinations resulted:

Q glycine soln Q water 1% overall propofol concentration 10% propofol0.51 4.50 0.51 4.50 13% propofol 0.41 4.65 0.41 4.65 16% propofol 0.324.69 0.31 4.71 19% propofol 0.29 4.72 0.28 4.73 2% overall propofolconcentration 10% propofol 1.01 4.08 1.01 4.06 13% propofol 0.77 4.320.78 4.28 16% propofol 0.62 4.38 0.60 4.42 19% propofol 0.53 4.48 0.554.48Each tube was allowed to sit overnight at room temperature(approximately 23 degrees Celsius), during which time the reverse cubicphases surrounded by water turned opaque white, while the reverse cubicphases surrounded by glycine remained clear and transparent. Each tubewas then inverted twice, and the liquid contents transferred to separate50 mL volumetric flasks and diluted to volume with mobile phase (50%acetonitrile, 40% water. 10% methanol, 0.5% phosphoric acid, all HPLCgrade solvents). The samples were mixed thoroughly and a portion of eachwas transferred to separate I-PLC vials. A standard solution wasprepared by dissolving 59.4 mg of Propofol reagent into 100 mL of mobilephase, mixing well, and transferring to vials. A check solution for thestandard was prepared in the same manner, using 52.1 mg of Propofol.

The standards and samples were analyzed on a Shimadzu SCL-10A VP HPLCsystem with the following chromatographic conditions: 25 cm×4.6 mmPhenomenex Luna C18 column, 2.0 mL/minute isocratic flow rate, 20 uLinjection volume, 14 minutes run length (propofol elution at 12minutes), and uv detection at 270 nm.

The system proved suitable for quantification with less than 0.5%relative standard deviation of five replicate injections of the standardsolution and all subsequent standard injections. Additionally, the checkstandard assayed at 100% of the standard solution.

The concentration of propofol in the aqueous phase was calculated withthe following equation:

${\left( \frac{samplepeakarea}{avgstdpeakarea} \right) \times \left( \frac{{concofstdsolution}\mspace{14mu} \left( \frac{59.4\mspace{14mu} {mg}}{100\mspace{14mu} {mL}} \right)}{\frac{volumeofaqueoussolution}{50\mspace{14mu} {mL}\mspace{11mu} {volumetricflask}}} \right) \times 100} = {\frac{ug}{mL}{propofol}}$

These data were graphed as micrograms/mL propofol in the aqueous phaseversus percent propofol in the cubic phase. The value for 13% propofolin the cubic phase at 1% with glycine is clearly an outlier.

% prop in Q 1% (gly) 2% (gly) 1% (water) 2% (water) 10 18.6 19.3 25.119.5 13 (34.9) 25 29.6 28.8 16 30.1 29.3 39.1 34.2 19 35.5 35.9 46.945.6

This Example thus shows that the level of aqueous propofol can besubstantially reduced by the use of high partition coefficient(high-Kow) diluent as described above, as well as showing the surprisingresult that the use of glycine can not only reduce the level of aqueousdrug, but also improve the compatibility of the reversed cubic phasewith the aqueous phase, as evidenced by the clarity of the glycinesamples in contrast with the non-glycine samples which showedsignificant turbidity in the cubic phase.

Example 19

In this Example, dogs were dosed with the formulation reported inExample 1 above, and this formulation was found to perform as well as,and similarly to, a currently marketed, emulsion-based formulation ofpropofol, Propoflo®. The cubic phase formulation, however, offers theadvantages of being essentially free of microbial growth-supportingcomponents.

On 3 consecutive days, six beagle dogs (approximately 1.5-3.5 years ofage) were dosed with Propoflo® (a commercially available propofolformulation) and Lyotropic PF1 in a 3-way crossover design. The dogswere on a controlled feeding schedule, receiving approximately 500 gramsof Certified Canine Diet (5507) for approximately 7 days prior to theinitiation of dosing. Food was withheld overnight prior to each dosingsession. Levels of contaminants known to be present in the feed andwater were thought to he incapable of interfering with this study. Youngadult used in this study were acclimated to laboratory conditions for atleast 14 days prior to animal phase initiation. Six dogs were selectedon the basis of general appearance and assigned to the following groups:

Group Dose Conc. Number Test Article Dose mg/kg Mg/mL No. of AnimalsCBG1 Lyotropic PF1 6.0 10 2 CBG3 Propoflo ® 6.0 10 2

The cubic phase dispersion (Lyocell®″) test articles of the instantinvention were stored at approximately 2-8 C and protected from light.The Propoflo® was obtained from Abbott Laboratories and stored at roomtemperature. Body weights were obtained just prior to doseadministration and were used as the basis for dosing. Clinicalobservations for mortality and general appearance were performed atleast twice a day following dose administration. Parameters forevaluation included postdosing observations. All animals were constantlyattended from the induction of anesthesia until emergence (i.e. standingon all four paws). The length of time from injection (start to finish;approximately 30 seconds) to induction, time to emergence, and time torising to four paws was recorded for each dog. The animals werecontinually monitored to assess level of anesthesia using jaw tone,palpebral and toe pinch reflexes.

No mortality occurred during the dosing or post dosing periods. Relevantrespiration characteristics or disturbances included the occurrence ofirregular respiration, apnea, dyspnea, and mild regurgitation (in 2 dogsonly). However, none of these disturbances could be considered to betest article specific since all of these occurred at an equal frequencywith all three test articles. After the start of the injection,induction of anesthesia occurred within 1 minute after the start of theinjection and could be described as a smooth induction regardless oftest article. In most cases, dogs injected with the cubic phasepreparations behaved similar (i.e., respiration characteristics, reflexevents, and postdosing observations) to those injected with commerciallyavailable Propoflo® preparation.

Individual Body Weight and dosing Records Animal Dose No. Body Concen-Dose Prefix: USDA Test Weight Dose tration Volume CBG Number Article(kg) (mg/kg) (mg/mL) (mL) Day 1 1M1 3643590 PF1 19.80 6 10 11.9 1F24220196 PF1 7.60 6 10 4.6 3M5 3645771 Propoflo 12.60 6 10 7.6 3F64119177 Propoflo 10.05 6 10 6.1 Day 2 2M3 3771687 Propoflo 15.25 6 109.2 2F4 4121538 Propoflo 9.10 6 10 5.5 3M5 3645771 PF1 12.25 6 10 7.43F6 4119177 PF1 10.15 6 10 6.1 Day 3 1M1 3643590 Propoflo 19.85 6 1012.0 1F2 4220196 Propoflo 7.55 6 10 4.6 2M3 3771687 PF1 15.25 6 10 9.22F4 4121538 PF1 9.00 6 10 5.4

Individual Predose Heart Rates Animal No. USDA Heart Rate Prefix: CBGNumber Test Article (BPM) Day 1 1M1 3643590 PF1 90 1F2 4220196 PF1 1203M5 3645771 Propoflo 126 3F6 4119177 Propoflo 90 Day 2 1M1 3643590 PF190 1F2 4220196 PF1 120 3M5 3645771 Propoflo 120 3F6 4119177 Propoflo 90Day 3 1M1 3643590 Propoflo 102 1F2 4220196 Propoflo 60 2M3 3771687 PF176 2F4 4121538 PF1 102

Individual Postdose Respiration Characteristics Animal No. USDA TestPrefix: CBG Number Article Respiration Characteristics Day 1 1M1 3643590PF1 Irregular respiration, rapid initially; then regular 1F2* 4220196PF1 Period of dyspnea, irregular respiration, apnea 3M5 3645771 PropofloRegular respiration throughout episode 3F6 4119177 Propoflo Regularrespiration with occasional apnea *Regurgitation noted at approximately2 minutes following injection Day 2 2M3 3771687 Propoflo Regularrespiration throughout episode 2F4 4121538 Propoflo Initial period ofapnea 3M5* 3645771 PF1 Irregular respiration followed by apnea. Regularrespiration for remained of episode. 3F6 4119177 PF1 Regular respirationthroughout episode *Mild episode of regurgitation Day 3 1M1 3643590Propoflo Regular respiration throughout episode 1F2 4220196 PropofloRegular respiration throughout episode 2M3 3771687 PF1 Initially, markedperiod of apnea followed by regular respiration 2F4 4121538 PF1 Regularrespiration throughout episode

Anesthesia Log Day 1 Animal No. STER Prefix: USDA Test INJ to IND toEMER to to CBG Number Article IND EMER STER STAND 1M1 3643590 PF10:00:34 0:18:49 0:00:00 0:06:42 1F2 4220196 PF1 0:00:41 0:10:27 0:00:000:04:26 3M5 3645771 Propoflo 0:00:40 0:07:33 0:00:16 0:03:31 3F6 4119177Propoflo 0:00:29 0:10:29 0:00:10 0:01:23 1M1 3643590 PF1 0:00:34 0:19:230:19:23 0:26:05 1F2 4220196 PF1 0:00:41 0:11:08 0:11:08 0:15:34 3M53645771 Propoflo 0:00:40 0:08:13 0:08:29 0:12:00 3F6 4119177 Propoflo0:00:29 0:10:58 0:11:08 0:12:31 INJ = Injection time (start) IND =Induction time EMER = Emergence time STER = Sternal posturing time STAND= Standing time (four paws) Format = HH:MM:SS Each test article wasinjected over approximately 30 seconds

Individual Anesthesia Log Day 1 Animal No. Prefix: USDA Test INJ to INJto CBG Number Article ABSENCE PRESENCE Duration JAW TONE 1M1 3643590 PF10:00:48 0:19:23 0:18:35 1F2 4220196 PF1 0:01:48 0:04:53 0:03:05 3M53645771 Propoflo 0:00:55 0:05:57 0:05:02 3F6 4119177 Propoflo 0:00:520:07:14 0:06:22 PALPEBRAL 1M1 3643590 PF1 0:01:08 0:05:54 0:04:46 1F24220196 PF1 0:01:29 0:04:34 0:03:05 3M5 3645771 Propoflo 0:01:55 0:03:500:01:55 3F6 4119177 Propoflo 0:01:10 0:05:28 0:04:18 TOE PINCH 1M13643590 PF1 0:00:57 0:18:59 0:18:02 1F2 4220196 PF1 0:02:39 0:04:460:02:07 3M5 3645771 Propoflo 0:01:15 0:05:30 0:04:15 3F6 4119177Propoflo 0:00:56 0:06:54 0:05:58 INJ = Injection time (start) ABSENCE =Loss of reflex PRESENCE = Regaining of reflex following loss Format =HH:MM:SS Each test article was injected over approximately 30 seconds

Individual Anesthesia Log Day 2 Animal No. STER Prefix: USDA Test INJ toIND to EMER to to CBG Number Article IND EMER STER STAND 2M3 3771687Propoflo 0:00:15 0:09:35 0:02:52 0:2:40  2F4 4121538 Propoflo 0:00:300:05:05 0:00:30 0:01:45 3M5 3645771 PF1 0:00:25 0:16:31 0:07:04 0:03:543F6 4119177 PF1 0:00:20 0:19:47 0:02:47 0:02:20 Animal No. Prefix: USDATest INJ to INJ to INJ to INJ to CBG Number Article IND EMER STER STAND2M3 3771687 Propoflo 0:00:15 0:09:50 0:12:42 0:15:22 2F4 4121538Propoflo 0:00:30 0:05:35 0:06:05 0:07:50 3M5 3645771 PF1 0:00:25 0:16:560:24:00 0:27:54 3F6 4119177 PF1 0:00:20 0:20:07 0:22:54 0:25:14 INJ =Injection time (start) IND = Induction time EMER = Emergence time STER =Sternal posturing time STAND = Standing time (four paws) Format =HH:MM:SS Each test article was injected over approximately 30 seconds

Individual Anesthesia Log Day 2 Animal No. Prefix: USDA Test INJ to INJto CBG Number Article ABSENCE PRESENCE Duration JAW TONE 1M1 3643590 PF10:00:57 0:18:59 0:18:02 1F2 4220196 PF1 0:02:39 0:04:46 0:02:07 3M53645771 Propoflo 0:01:15 0:05:30 0:04:15 3F6 4119177 Propoflo 0:00:560:06:54 0:05:58 PALPEBRAL 2M3 3771687 Propoflo 0:00:43 0:06:24 0:05:412F4 4121538 Propoflo 0:01:35 0:05:05 0:03:30 3M5 3645771 PF1 0:01:570:09:30 0:07:33 3F6 4119177 PF1 0:01:37 0:15:37 0:14:00 TOE PINCH 2M33771687 Propoflo 0:00:58 0:06:24 0:05:26 2F4 4121538 Propoflo 0:00:450:05:05 0:04:20 3M5 3645771 PF1 0:00:50 0:09:20 0:08:30 3F6 4119177 PF10:00:40 0:16:00 0:15:20 INJ = Injection time (start) ABSENCE = Loss ofreflex PRESENCE = Regaining of reflex following loss Format = HH:MM:SSEach test article was injected over approximately 30 seconds

Individual Anesthesia Log Day 3 Animal No. STER Prefix: USDA Test INJ toIND to EMER to to CBG Number Article IND EMER STER STAND 1M1 3643590Propoflo 0:00:24 0:13:42 0:00:13 0:00:24 1F2 4220196 Propoflo 0:00:290:08:41 0:01:00 0:00:19 2M3 3771687 PF1 0:00:22 0:16:01 0:06:45 0:00:312F4 4121538 PF1 0:00:42 0:13:00 0:05:56 0:00:22 1M1 3643590 Propoflo0:00:24 0:14:06 0:14:19 0:14:43 1F2 4220196 Propoflo 0:00:29 0:09:100:10:10 0:10:29 2M3 3771687 PF1 0:00:22 0:16:23 0:23:08 0:23:39 2F44121538 PF1 0:00:42 0:13:42 0:19:38 0:20:00 INJ = Injection time (start)IND = Induction time EMER = Emergence time STER = Sternal posturing timeSTAND = Standing time (four paws) Format = HH:MM:SS Each test articlewas injected over approximately 30 seconds

Individual Anesthesia Log Day 3 Animal No. Prefix: USDA Test INJ to INJto CBG Number Article ABSENCE PRESENCE Duration JAW TONE 1M1 3643590Propoflo 0:01:06 0:12:45 0:11:39 1F2 4220196 Propoflo 0:01:30 0:07:070:05:37 2M3 3771687 PF1 0:00:44 0:14:15 0:13:31 2F4 4121538 PF1 0:02:260:13:02 0:10:36 PALPEBRAL 1M1 3643590 Propoflo 0:00:45 0:16:25 0:15:401F2 4220196 Propoflo 0:01:15 0:07:07 0:05:52 2M3 3771687 PF1 0:00:440:13:00 0:12:16 2F4 4121538 PF1 0:01:20 0:09:05 0:07:45 TOE PINCH 1M13643590 Propoflo 0:00:53 0:09:54 0:09:01 1F2* 4220196 Propoflo * * * 2M33771687 PF1 0:00:44 0:13:15 0:12:31 2F4 4121538 PF1 0:01:18 0:09:500:08:32 *Toe Pinch reflex remained positive throughout episode INJ =Injection time (start) IND = Induction time EMER = Emergence time STER =Sternal posturing time STAND = Standing time (four paws) Format =HH:MM:SS Each test article was injected over approximately 30 seconds.

Example 20

A reversed cubic phase containing the anesthetic propofol was firstprepared by mixing 1.496 grams of propofol (Albemarle Corporation, BatonRouge, La.) 1.346 gm of vitamin E (Aldrich Chemical Company, Milwaukee,Wis.), 3.902 gm of sterile water (Abbott Laboratories, Chicago, Ill.),and 8.255 gm of Pluronic L122 (Ethox Chemicals, Greenville, S.C.). Afterthoroughly mixing this composition, it was checked that the material wasoptically isotropic and of high viscosity. Next, 0.504 gm of the anionicsurfactant deoxycholic acid sodium salt (Aldrich Chemical Company,Milwaukee, Wis.) and 1.500 gm of glycine (Spectrum Chemical Company,Gardena, Calif.) was dissolved in 88 mL water. Then, 10.101 gm of thecubic phase was added to the 250 ml beaker containing the surfactantsolution and dispersed using a homogenizer (Brinkmann Polytron PT 3000)at 29 k rpm for 20 minutes. The pH of the mixture was adjusted to 7.40by the addition of 5 pipette droplets of 1M hydrochloric acid (SigmaChemical Company, St. Louis, Mo.). The dispersion was injected intosterile vials using a 27 gauge needle attached to a 0.22 μm PVDF syringefilter (Millipore, Ireland). Each vial was sparged with nitrogen for 5minutes to remove oxygen from the dispersion. Observation in aReichert-Jung Polyvar microscope operating in differential interferencecontrast (DIC) mode demonstrated that a particle size on the order of200 nanometers had been achieved. The dispersion was then analyzed usinga Beckman Coulter DELSA 440SX for Doppler Electrophoretic LightScattering Analysis, set in zeta potential measurement mode. Thedispersion was diluted 4:1 water to dispersion in order to get thedetector levels on scale. The resulting measured zeta potentialdistribution, using four angles of measurement, shows the distributioncentered around −34 mV, which is a strong enough zeta potential toproduce a stable dispersion. The concentration of propofol in thisdispersion, referred to below as Lyotropic PH(1%), was 1% or 10 mg/mL.

A reversed cubic phase containing the anesthetic propofol was firstprepared by mixing 2.206 grams of propofol (Albemarle Corporation, BatonRouge, La.) 1.982 gm of vitamin E (Aldrich Chemical Company, Milwaukee,Wis.), 5.739 gm of sterile water (Abbott Laboratories, Chicago, Ill.),and 12.100 gm of Pluronic L122 (Ethox Chemicals, Greenville, S.C.).After thoroughly mixing this composition, it was checked that thematerial was optically isotropic and of high viscosity. Next, 1.003 gmof the anionic surfactant deoxycholic acid sodium salt (Aldrich ChemicalCompany, Milwaukee, Wis.) and 1.502 gm of glycine (Spectrum ChemicalCompany, Gardena, Calif.) was dissolved in 77.5 mL water. Then, 19.989gm of the cubic phase was added to the 250 ml beaker containing thesurfactant solution and dispersed using a homogenizer (BrinkmannPolytron PT 3000) at 29 k rpm for 30 minutes. The pH of the mixture wasadjusted to 7.40 by the addition of 6 pipette droplets of 1Mhydrochloric acid (Sigma Chemical Company, St. Louis, Mo.). Thedispersion was injected into sterile vials using a 27 gauge needleattached to a 0.22 μm PVDF syringe filter (Millipore, Ireland). Eachvial was sparged with nitrogen for 5 minutes to remove oxygen from thedispersion. Observation in a Reichert-Jung Polyvar microscope operatingin differential interference contrast (DIC) mode demonstrated that aparticle size on the order of 200 nanometers had been achieved. Thedispersion was then analyzed using a Beckman Coulter DELSA 440SX forDoppler Electrophoretic Light Scattering Analysis, set in zeta potentialmeasurement mode. The dispersion was diluted 4:1 water to dispersion inorder to get the detector levels on scale. The resulting measured zetapotential distribution, using four angles of measurement, shows thedistribution centered around −32 mV, which is a strong enough zetapotential to produce a stable dispersion. The concentration of propofolin this dispersion, referred to below as Lyotropic PF1(2%), was 2% or 20mg/mL.

Dogs were dosed with the above two formulations, and each was found toperform as well as or better than, and similarly to, a currentlymarketed, emulsion-based formulation of propofol, Propoflo® (AbbotLabs).

On 3 consecutive days, six beagle dogs (approximately 1.5-3.5 years ofage) were dosed with either Propoflo® (a commercially available propofolformulation) or Lyotropic. PFI(1%) or Lyotropic PF1(2%) in a 3-wayrandomized crossover design. The dogs were on a controlled feedingschedule, receiving approximately 500 grams of Certified Canine Diet(5507) for approximately 7 days prior to the initiation of dosing. Foodwas withheld overnight prior to each dosing session. Levels ofcontaminants known to be present in the feed and water were thought tobe incapable of interfering with this study. The animals used in thisstudy were acclimated to laboratory conditions for at least 14 daysprior to animal phase initiation. Six dogs (3 male and 3 female) wereselected on the basis of general appearance.

The cubic phase dispersion (“LyoCell®”) test articles of the instantinvention were stored at approximately 2-8° C. and protected from light.The Propoflo® was obtained from Abbott Laboratories and stored at roomtemperature. Body weights were obtained just prior to doseadministration and were used as the basis for dosing, and all dogs weredosed at 6.0 mg/mL for each of the three formulations. Clinicalobservations for mortality and general appearance were performed atleast twice a day following dose administration. Parameters forevaluation included post dosing observations. All animals wereconstantly attended from the induction of anesthesia until emergence(i.e. standing on all four paws). The length of time from injection(start to finish; approximately 30 seconds) to induction, emergence,sternal posturing and rising to four paws was recorded for each dog. Theanimals were continually monitored to assess level of anesthesia usingjaw tone, palpebral and toe pinch reflexes. No mortality occurred duringthe dosing or post dosing periods. Relevant respiration characteristicsor disturbances included the occurrence of irregular respiration, apnea,dyspnea, and mild regurgitation (in 1 dog only). Induction of anesthesiaoccurred within 1 minute after the start of the injection and could bedescribed as a smooth induction regardless of test article. In mostcases, dogs injected with the cubic phase preparations behaved similar(i.e., respiration characteristics, reflex events, and post dosingobservations) to those injected with commercially available Propoflo®.

Individual Post dose respiration characteristics Pre-Dose Heart USDARate Day Number Test Article (bpm) Respiration Characteristics 1 4365500PF1 (1%) 90 Initial period of rapid shallow breathing; then regularbreathing, pattern 1 4175654 PF1 (1%) 96 Regular breathing pattern 14169859 PF1 (2%) 108 Regular breathing pattern. Regurgitation at 30 secpost dose, at 35 min 45 sec post dose, and 1:17:00 post dose 1 4372646PF1 (2%) 72 Initial period of apnea, then regular breathing pattern 24365500 Propoflo ® 90 Regular breathing pattern 2 4175654 Propoflo ® 96Regular breathing pattern 2 4169859 PF1 (1%) 102 Initial period of rapidshallow breathing; then regular breathing pattern 2 4372646 PF1 (1%) 66Initial period of rapid shallow breathing; then regular breathingpattern 2 4361270 PF1 (2%) 96 Initial period of rapid shallow breathing;then regular breathing pattern 2 4360206 PF1 (2%) 78 Initial period ofrapid shallow breathing; then regular breathing pattern 3 4365500 PF1(2%) 102 Initial period of apnea, then regular breathing pattern 34175654 PF1 (2%) 78 Initial period of rapid shallow breathing; thenregular breathing pattern 3 4169859 Propoflo ® 90 Regular breathingpattern 3 4372646 Propoflo ® 72 Regular breathing pattern 3 4361270 PF1(1%) 66 Initial period of apnea, then rapid shallow breathing, thenregular breathing pattern 3 4360206 PF1 (1%) 84 Regular breathingpattern 4 4361270 Propoflo ® 78 Regular breathing pattern 4 4360206Propoflo ® 72 Regular breathing pattern

Anesthesia Log Animal USDA INJ to INJ to Number Number Test Article INDEMER Propoflo ® 1M1 4365500 Propoflo ® 0:00:33 0:08:09 1F4 4175654Propoflo ® 0:00:25 0:06:58 2M2 4169859 Propoflo ® 0:00:32 0:20:49 2F54372646 Propoflo ® 0:00:24 0:15:43 3M3 4361270 Propoflo ® 0:00:250:13:22 3F6 4360206 Propoflo ® 0:00:24 0:08:05 AVERAGE 0:00:27 0:12:11STD DEV 0:00:04 0:05:27 PF1 (1%) 1M1 4365500 PF1 (1%) 0:00:33 0:22:301F4 4175654 PF1 (1%) 0:00:30 0:19:01 2M2 4169859 PF1 (1%) 0:00:300:17:00 2F5 4372646 PF1 (1%) 0:00:27 0:18:01 3M3 4361270 PF1 (1%)0:00:25 0:19:23 3F6 4360206 PF1 (1%) 0:00:37 0:18:38 AVERAGE 0:00:300:19:05 STD DEV 0:00:04 0:01:52 PF1 (2%) 2M2 4169859 PF1 (2%) 0:00:440:34:19 2F5 4372646 PF1 (2%) 0:00:26 0:33:50 3M3 4361270 PF1 (2%)0:00:40 0:20:39 3F6 4360206 PF1 (2%) 0:00:35 0:29:12 1M1 4365500 PF1(2%) 0:00:34 0:09:22 1F4 4175654 PF1 (2%) 0:00:26 0:17:06 AVERAGE0:00:34 0:24:05 STD DEV 0:00:07 0:10:02

Summary of Anesthesia Log Propoflo ® PF1 (1%) PF1 (2%) INJ to IND0:00:27 0:00:30 0:00:34 INJ to EMER 0:12:11 0:19:05 0:24:05 INJ =Injection time (start) IND = Induction time EMER = Emergence time Format= HH:MM:SS Each test article was injected over approximately 30 seconds

Example 21

The following example describes a charge-stabilize liquid crystallinedispersion containing the local anesthetic drug bupivacaine. Working ina laminar flow hood, 0.900 grams of the local anesthetic bupivacaine, inits free base form, were dissolved in 3.64 gm of alpha-tocopherol(Aldrich Chemical Company, Milwaukee, Wis.) by heating to 55° C.Following dissolution, 1.820 gm of sterile water (Abbott Laboratories,Chicago, Ill.) and 3.640 gm of Pluronic P123 (BASF Corporation, Mt.Olive, N.J.) was added to the vitamin E. The components were mixed toform a reversed cubic phase that was optically isotropic and of highviscosity. Next, 0.402 gm of sodium deoxycholate (Aldrich ChemicalCompany, Milwaukee, Wis.) was dissolved in 39.6 ml of sterile water. Anamount 8.048 gm of cubic phase was dispersed in the sodium deoxycholatesolution, first using the homogenizer (Brinkmann Polytron PT 3000) at 29k rpm for 1 minute, then using the microfluidizer (Micofluidics ModelM110L) at approximately 15,000 psi for five 1.5 minute runs. Thedispersion, referred to as “Lyotropic/F4C,” was injected into sterilevials using a 27 gauge needle attached to a 0.45 μm PVDF syringe filter(Millipore, Ireland).

Lyotropic/F4C was analyzed using a Beckman Coulter N4 PLUS submicronparticle size analyzer. A drop of the dispersion was diluted in wateruntil an adequate measurement intensity level was obtained. FIG. 15illustrates the results of a particle size analysis with a five minuteequilibration time and a three minute run time. All of the particles inthe dispersion are less than 400 nm. Additionally, Lyotropic/F4C wasanalyzed using a Beckman Coulter DELSA 440SX for Doppler ElectrophoreticLight Scattering Analysis, set in zeta potential measurement mode. FIG.16 shows the measured zeta potential distribution, using four angles ofmeasurement. At all four angles, the distribution is centered at −31 mV,which is a strong enough zeta potential to produce a stable dispersion.The above formulation was tested in the rat “Paw Withdrawal” model todetermine the duration of analgesia. Male Spraque-Dawley rats, weighing400-450 gm, were studied at two dose levels: 1.0 mg/kg and 3.0 mg/kg.All rats were housed under standard conditions in accordance to AALACguidelines, with access to food and water ad libitum. Six hours prior toevaluation, food was withheld.

PROCEDURES: Each rat was briefly anesthetized by exposure to theinhalational agent halothane in order to facilitate animal handling andto ensure precise injection of the test and control agents. Onceunconscious, a small incision in the region of the popliteal fossa ofthe hind limb was made. Exposure of the sciatic nerve was obtained withminimal retraction. Utilizing an appropriately sized needle and syringe,either the bupivacaine-LyoCell® formulation or the standard bupivacainehydrochloride was injected into the perineurium of the sciatic nerve.The incision was then closed with an appropriately sized surgical clip.

Local anesthetic blockade to thermal nociception was determined byexposure of the hind paw of the treated hind limb to the heated surfaceof a thermal plantar testing apparatus. Surface temperatures weremaintained in a range from 50 to 54 degree C. The latency period to paywithdrawal from the heated surface was recorded by digital timer.Baseline latency period was found to be approximately 1 to 3 seconds innon-anesthetized hind paws. In an attempt to minimize thermal injury tothe hind paw, maximum exposure to the thermal plantar testing apparatuswas limited to 12 seconds. Latency periods exceeding 6 seconds wereconsidered indicative of analgesia to thermal testing.

Six rats were tested for latency withdrawal of the treated hind limbafter 30 minutes and 60 minutes, and then hourly for an additional fivehours. At a dose of 1 mg/kg dose of the cubic phase formulation, thesensor blocking effect lasted over 5 hours, for 4 of the 6 rats testedand over 6 hours for two of the six rats tested.

Example 22

This Example demonstrates the long-term physical stability ofdispersions of the instant invention. A cubic phase was first preparedby mixing 5.7176 grams of propofol, 7.8170 grams of water, and 16.5300grams of the poloxamer surfactant Ethox L-122 into a 50 mL test tube andstirring with a spatula until it was all one phase. In a 600 mL beakerwere placed 1.0533 grams of sodium deoxycholic acid, 400mL of distilledwater, and 21.0682 grams of the cubic phase. This was homogenized with aBrinkmann PT 10/35 homogenizer until the material was dispersed. Thiswas then microfluidized using a Microfluidics M110L for 10 runs of 1.5minutes each run. The dispersion was then injected into sterile vialsvia an 18 gauge needle.

Analysis of the pH, particle size (measured as described herein by aBeckmann N4 Plus particle sizer), and zeta potential (as described, witha DELSA analyzer) was performed at regular intervals over a period ofsix months. The 6-month data, reported in the table below, indicateexcellent stability for the particle dispersion.

Test Day 0 6 Months pH 8.1 7.9 Particle Size 132 nm 135 nm ZetaPotential −48 mV −34 mV

Example 23

A reversed cubic phase containing the anesthetic etomidate was preparedby dissolving 0.0200 grams of etomidate (Sigma Chemical Company, St.Louis, Mo.) in 0.300 gm of vitamin E (Aldrich Chemical Company,Milwaukee, Wis.) and adding 0.190 gm of distilled water and 0.488 gm ofPluronic L122 (Ethox Chemicals, Greenville, S.C.). After thoroughlymixing this composition, it was checked that the material was opticallyisotropic and of high viscosity. Next, 0.024 gm of the anionicsurfactant docusate sodium (Aldrich Chemical Company, Milwaukee, Wis.)was dissolved in 5.992 of of distilled water. Then, 0.605 gm of thecubic phase was added to the 50 mL beaker containing the surfactantsolution and dispersed using a homogenizer (Brinkmann PT 10/35) at speed10 for 10 minutes. The dispersion was injected into a sterile vial usinga 27 gauge needle attached to a 0.20 urn PTFE syringe filter (Millipore,Ireland). Observation in a Reichert-Jung Polyvar microscope operating indifferential interference contrast (DIC) mode demonstrated that aparticle size on the order of 200 nanometers had been achieved. Thedispersion was then analyzed using a Beckman Coulter DELSA 440SX forDoppler Electrophoretic Light Scattering Analysis, set in zeta potentialmeasurement mode. The resulting measured zeta potential distribution,using four angles of measurement, shows the distribution centered on−48.5 mV, which is a strong enough zeta potential to produce a stabledispersion. The concentration of etomidate in this dispersion was 0.2%or 2 mg/mL.

While the invention has been described in terms of its preferredembodiments, those skilled in the art will recognize that the inventioncan be practiced with modification within the spirit and scope of theappended claims. Accordingly, the present invention should not belimited to the embodiments as described above, but should furtherinclude all modifications and equivalents thereof within the spirit andscope of the description provided herein.

1-200. (canceled)
 201. A composition pharmaceutically acceptable forinjection in a mammal, comprising: (i) a plurality of uncoated,ionically charged particles comprising reversed cubic phase or reversedhexagonal phase material which includes at least one charged, bilayerassociated ingredient wherein a total of all charged, bilayer associatedingredients in the reversed cubic phase or reversed hexagonal phasematerial is between 0.02:1 and 0.08:1, and (ii) a liquid comprising apolar solvent, said uncoated, ionically charged particles beingstabilized in dispersion in said liquid, and said uncoated, ionicallycharged particles have a size of from 40 nm to 10 microns.
 202. Thecomposition of claim 201 further comprising at least one activeincorporated in said uncoated, ionically charged particles.
 203. Thecomposition of claim 202 wherein said at least one active is solubilizedin said reversed cubic phase or reversed hexagonal phase material. 204.The composition of claim 202 wherein said active is dissolved in saidreversed cubic phase or reversed hexagonal phase material.
 205. Thecomposition of claim 202 wherein said active is a liquid that isembedded, dissolved, dispersed or otherwise incorporated within saidreversed cubic phase or reversed hexagonal phase material.
 206. Thecomposition of claim 202 wherein said active is solubilized in a liquidthat is embedded, dissolved, dispersed or otherwise incorporated withinsaid reversed cubic phase or reversed hexagonal phase material.
 207. Thecomposition of claim 202 wherein said active is dispersed in saidreversed cubic phase or reversed hexagonal phase material in the form ofcrystals or an amorphous solid.
 208. The composition of claim 202wherein said active is a cancer therapeutic agent.
 209. The compositionof claim 208 wherein said active cancer therapeutic agent is selectedfrom the group consisting of camptothecins, taxanes, rubicins andamphotericin B.
 210. The composition of claim 202 wherein said active isa polypeptide.
 211. The composition of claim 202 wherein said active isa protein.
 212. The composition of claim 211 wherein said protein isselected from the group consisting of insulin and erythropoietin. 213.The composition of claim 202 wherein said active is an amino acid. 214.The composition of claim 202 wherein said active is a polysaccharide.215. The composition of claim 202 wherein said active is a lectin. 216.The composition of claim 202 wherein said active is an antibody. 217.The composition of claim 202 wherein said active is a receptor.
 218. Thecomposition of claim 202 wherein said active is a nucleic acid.
 219. Thecomposition of claim 202 wherein said active is a vitamin.
 220. Thecomposition of claim 202 wherein said active is a general anestheticagent.
 221. The composition of claim 220 wherein said general anestheticagent is selected from the group consisting of propofol, alphaxalone,alfadolone, eltanolone, propanidid, ketamine, pregnanolone, andetomidate.
 222. The composition of claim 220 wherein said generalanesthetic agent is propofol.
 223. The composition of claim 220 whereinsaid general anesthetic agent is etomidate.
 224. The composition ofclaim 220 wherein said active is a local anesthetic agent.
 225. Thecomposition of claim 224 wherein said local anesthetic agent is selectedfrom the group consisting of bupivacaine, lidocaine, procaine,tetracaine, mepivacaine, etidocaine, oxybuprocaine, cocaine, benzocaine,pramixine, prilocaine, proparacaine, ropivicaines, chloroprocaine, anddibucaine.
 226. The composition of claim 224 wherein said localanesthetic agent is bupivacaine.
 227. The composition of claim 202wherein said active is an anesthetic reversal agent.
 228. Thecomposition of claim 202 wherein said active is an enzyme.
 229. Thecomposition of claim 202 wherein said active is a radioactive agent.230. The composition of claim 202 wherein said active is a toxin. 231.The composition of claim 202 wherein said active is a steroid.
 232. Thecomposition of claim 202 wherein said active is a hormone.
 233. Thecomposition of claim 202 wherein said active is an immunogen.
 234. Thecomposition of claim 202 wherein said active is a vaccine adjuvant. 235.The composition of claim 202 wherein said active is a biomacromolecule.236. The composition of claim 202 wherein said active is an agonist.237. The composition of claim 202 wherein said active is an antagonist.238. The composition of claim 202 wherein said active is a bioactiveagent.
 239. The composition of claim 202 wherein said active is amedicament.
 240. The composition of claim 202 wherein said active is anonsteroidal anti-inflammatory agent.
 241. The composition of claim 202wherein said nonsteroidal anti-inflammatory agent is selected from thegroup consisting of salicylates, para-aminophenol derivatives,acetaminophen, fenomates, proprionic acid derivatives, naproxen andibuprofen.
 241. The composition of claim 202 wherein said active isselected from the group consisting of coenzyme Q10, benzodiazepines,diazepam, and barbiturates.
 242. The composition of claim 202 whereinsaid active is an amide or an ester.
 243. The composition of claim 202wherein said active is a photodynamic therapy agent
 244. The compositionof claim 202 wherein said active is a radiopaque or optically densematerial used for imaging.
 202. The composition of claim 202 whereinsaid reversed cubic phase or reversed hexagonal phase material comprisesphosphatidylcholine.
 246. The composition of claim 202 wherein saidreversed cubic phase or reversed hexagonal phase material comprises apluronic with less than 30% PEO groups by weight.
 247. The compositionof claim 202 further comprising an essential oil.
 248. The compositionof claim 201 wherein said particle zeta potential has a magnitudegreater than or equal to 25 millivolts.
 249. The composition of claim201 wherein said charged bilayer associated ingredient is selected fromthe group consisting of eugenol, isoeugenol, quinolines,hydroxyquinolines, benzoquinolines, tricyclics, pigments, chlorophyll,natural oil extracts, biosurfactants, dyes, gramicidin, casein, albumin,glycoproteins, lipid-anchored proteins, receptor proteins, proteinase A,amyloglucosidase, enkephalinase, dipeptidyl peptidase IV, gamma-glutamyltransferase, galactosidase, neuraminidase, alpha-mannosidase,cholinesterase, arylamidase, surfactin, ferrochelatase, spiralin,penicillin-binding proteins, microsomal glycotransferases, kinases,bacterial outer membrane proteins, and histocompatibility antigens. 250.The composition of claim 201 wherein said charged bilayer associatedingredient is a salt of a deoxycholic acid or a related cholate. 251.The composition of claim 250 wherein said salt is glycocholate.
 252. Thecomposition of claim 201 wherein said charged bilayer associatedingredient is a charged surfactant.
 253. The composition of claim 201wherein said charged bilayer associated ingredient is an active. 254.The composition of claim 202 wherein said reversed cubic phase orreversed hexagonal phase material comprises a high partition coefficientdiluent.
 255. The composition of claim 254 wherein said high partitioncoefficient diluent is selected from the group consisting oftocopherols, benzyl benzoate, estragole, eugenol, isoeugenol, linalool,strawberry aldehyde, terpineol, and the following essential oils: balsamof Peru, basil, bay, bois de rose (rosewood), carrot seed, clovebud,eucalyptus, ginger, grapefruit, hyssop, lemon, mugwort, myrrh gum,bitter orange, oregano, palmarosa, patchouly, peppermint, petitgrain,rosemary, santalwood oil, spearmint, thuja (cedar leaf), thyme, vanilla,and ylang ylang (cananga).
 256. The composition of claim 201 whereinsaid particle zeta potential has a magnitude greater than 30 millivolts.257. The composition of claim 201 wherein said particle zeta potentialhas a magnitude greater than 45 millivolts.
 258. The composition ofclaim 201 wherein said particle zeta potential has a magnitude greaterthan 55 millivolts.
 259. The composition of claim 201 wherein saidreversed cubic phase or reversed hexagonal phase material includesphosphatidylcholine and further comprising tocopherol.
 260. Thecomposition of claim 202 further comprising a targeting moietyassociated with said uncoated, charged particles.